Measurement of fluid delivery

ABSTRACT

A method for determining a volume of fluid dispensed into a test housing includes creating an electrical potential across at least one input electrode of a plurality of input electrodes and at least one output electrode of a plurality of output electrodes. The input electrodes and the output electrodes are each coupled to the test housing. The method includes receiving at least one signal from the at least one output electrode based on the fluid dispensed into the test housing. The method includes calculating the volume of fluid dispensed into the test housing based on the at least one signal received from the at least one output electrode, a dimension associated with an internal channel defined within the test housing, and a distance between two input electrodes of the plurality of input electrodes.

CROSS-REFERENCE TO PRIORITY APPLICATION(S)

This application is a continuation of U.S. patent application Ser. No.16/939,525 filed Jul. 27, 2020 which is a continuation of U.S. patentapplication Ser. No. 16/158,225 filed Oct. 11, 2018. The relevantdisclosure of the above applications are incorporated herein byreference.

TECHNICAL FIELD

Embodiments of the subject matter described herein relate generally tomeasuring a fluid delivery by a medical device. More particularly,embodiments of the subject matter relate to electrofluidic measurementof a fluid delivery by a fluid infusion device, such as an insulininfusion device.

BACKGROUND

Certain diseases or conditions may be treated, according to modernmedical techniques, by delivering a medication or other substance to thebody of a user, either in a continuous manner or at particular times ortime intervals within an overall time period. For example, diabetes iscommonly treated by delivering defined amounts of insulin to the user atappropriate times. Some common modes of providing insulin therapy to auser include delivery of insulin through manually operated syringes andinsulin pens. Other modern systems employ programmable fluid infusiondevices (e.g., insulin pumps) to deliver controlled amounts of insulinto a user.

A fluid infusion device suitable for use as an insulin pump may berealized as an external device or an implantable device, which issurgically implanted into the body of the user. External fluid infusiondevices include devices designed for use in a generally stationarylocation (for example, in a hospital or clinic), and devices configuredfor ambulatory or portable use (to be carried by a user). External fluidinfusion devices may establish a fluid flow path from a fluid reservoirto the patient via, for example, a set connector of an infusion set,which is coupled to the fluid reservoir.

Delivery accuracy of the fluid infusion device is necessary to ensurethat the patient receives the correct amount of insulin. Generally, eachfluid infusion device is subjected to testing to ensure that the amountof fluid delivered by the fluid infusion device is accurate. Currenttest methods rely on a gravimetric balance. Due to the small amount offluid delivered by the fluid infusion device, the measurement of thefluid delivered using the gravimetric balance may be influenced byexternal factors, such as temperature of the testing environment,evaporation, vibrations, humidity and air density.

Accordingly, it is desirable to provide systems and methods formeasuring a delivery of a fluid by a fluid infusion device, such as aninsulin infusion device. Moreover, it is desirable to provide systemsand methods for measuring an amount of fluid delivered by a fluidinfusion device that is resistant to external factors. Furthermore,other desirable features and characteristics will become apparent fromthe subsequent detailed description and the appended claims, taken inconjunction with the accompanying drawings and the foregoing technicalfield and background.

BRIEF SUMMARY

In various embodiments, a test system for measuring a volume of fluiddispensed by a fluid infusion device is provided. The test systemincludes a test housing. The test housing includes an inlet and aninternal channel. The inlet is to be coupled to the fluid infusiondevice to receive the volume of fluid, and the internal channel is influid communication with the inlet. The test system includes an inputelectrode coupled to the internal channel to be in fluid communicationwith the volume of fluid, and an output electrode coupled to theinternal channel to be in fluid communication with the volume of fluid.The output electrode is coupled to the internal channel so as to bespaced apart from the input electrode. The test system includes a powersource configured to create a voltage potential between the inputelectrode and the output electrode. The volume of fluid in the internalchannel conducts current between the input electrode and the outputelectrode to facilitate measurement of the volume of fluid dispensed bythe fluid infusion device.

Also provided according to various embodiments is a test system formeasuring a volume of fluid dispensed by a fluid infusion device. Thetest system includes a test housing. The test housing includes an inletand an internal channel. The inlet is to be coupled to the fluidinfusion device to receive the volume of fluid, and the internal channelis in fluid communication with the inlet. The test system includes aplurality of input electrodes coupled to the internal channel to be influid communication with the volume of fluid, and a plurality of outputelectrodes coupled to the internal channel to be in fluid communicationwith the volume of fluid. The plurality of output electrodes is spacedapart from a respective one of the plurality of input electrodes. Thetest system includes a power source configured to apply a voltage to arespective one of the plurality of input electrodes. The volume of fluidin the internal channel conducts current between the respective one ofplurality of input electrodes and a respective at least one of theplurality of output electrodes to facilitate measurement of the volumeof fluid dispensed by the fluid infusion device.

Further provided is a test system for measuring a volume of fluiddispensed by a fluid infusion device. The test system includes a testhousing. The test housing includes an inlet and an internal channel. Theinlet is to be coupled to the fluid infusion device to receive thevolume of fluid, and the internal channel is in fluid communication withthe inlet. The test system includes a plurality of input electrodescoupled to the internal channel to be in fluid communication with thevolume of fluid, and a plurality of output electrodes coupled to theinternal channel to be in fluid communication with the volume of fluid.Each one of the plurality of output electrodes is spaced apart from arespective one of the plurality of input electrodes. The test systemincludes a power source configured to apply a voltage to a respectiveone of the plurality of input electrodes. The volume of fluid in theinternal channel conducts current between a respective one of pluralityof input electrodes and a respective at least one of the plurality ofoutput electrodes to facilitate measurement of the volume of fluiddispensed by the fluid infusion device. Each of the plurality of inputelectrodes has an end that extends into the internal channel to be incommunication with the fluid, and each of the plurality of outputelectrodes has a second end that extends into the internal channel thatis spaced apart from the end of the respective one of the plurality ofinput electrodes such that a gap is defined within the internal channelbetween the end of the respective one of the plurality of inputelectrodes and the second end of respective one of the plurality ofoutput electrodes.

Also provided according to various embodiments is a method fordetermining a volume of fluid dispensed into a test housing. The methodincludes controlling, by a processor, a power source to create a voltagepotential across an input electrode arrangement and an output electrodearrangement associated with the input electrode arrangement each coupledto the test housing. The method includes receiving, by the processor, asignal from the output electrode arrangement based on the fluid receivedinto the test housing, and calculating, by the processor, the volume offluid dispensed into the test housing based on the signal received fromthe output electrode arrangement. The method includes generating, by theprocessor, a user interface for display on a display that illustratesthe volume of fluid dispensed, and displaying the generated userinterface on the display.

Further provided is a test control system for determining a volume ofdispensed fluid. The test control system includes a test housing. Thetest housing includes an inlet and an internal channel. The inlet is toreceive the volume of fluid, and the internal channel is in fluidcommunication with the inlet. The test control system includes an inputelectrode arrangement coupled to the test housing, and an outputelectrode arrangement associated with the input electrode arrangementand coupled to the test housing so as to be spaced apart from the inputelectrode arrangement. The test control system includes a controller,having a processor, that is configured to: control a power source tosupply a voltage to the input electrode arrangement; receive a signalfrom the output electrode arrangement based on the fluid received intothe test housing; calculate the volume of fluid dispensed into the testhousing based on the signal received from the output electrodearrangement; generate a user interface for display on a display thatillustrates the volume of fluid dispensed; and display the generateduser interface on the display.

Also provided is a method for determining a volume of fluid dispensedinto a test housing. The method includes controlling, by a processor, apower source to create a voltage potential across at least one of aplurality of input electrodes and a respective at least one of aplurality of output electrodes. The plurality of input electrodes andthe plurality of output electrodes are each coupled to the test housing.The method includes receiving, by the processor, a signal from therespective at least one of the plurality of output electrodes based onthe fluid received into the test housing. The method includescalculating, by the processor, the volume of fluid dispensed into thetest housing based on the signal received from the respective at leastone of the plurality of output electrodes, a dimension associated withan internal channel defined within the test housing, and a distancebetween each one of the plurality of input electrodes.

Further provided is a test control system for determining a volume ofdispensed fluid. The test control system includes a test housing thatincludes an inlet and an internal channel. The inlet to receive thevolume of fluid, and the internal channel is in fluid communication withthe inlet. The test control system includes a plurality of inputelectrodes coupled to the test housing, and a plurality of outputelectrodes coupled to the test housing so as to be spaced apart from theplurality of input electrodes. Each one of the plurality of inputelectrodes is associated with a respective at least one of the pluralityof output electrodes. The test control system includes a controller,having a processor, that is configured to: control a power source tosupply a voltage to at least one of the plurality of input electrodes;receive a signal from the respective at least one of the plurality ofoutput electrodes based on the fluid received into the test housing; andcalculate the volume of fluid dispensed into the test housing based onthe signal received from the respective at least one of the plurality ofoutput electrodes, a dimension associated with the internal channel, anda distance between each one of the plurality of input electrodes.

This summary is provided to introduce a selection of concepts in asimplified form that are further described below in the detaileddescription. This summary is not intended to identify key features oressential features of the claimed subject matter, nor is it intended tobe used as an aid in determining the scope of the claimed subjectmatter.

BRIEF DESCRIPTION OF THE DRAWINGS

A more complete understanding of the subject matter may be derived byreferring to the detailed description and claims when considered inconjunction with the following figures, wherein like reference numbersrefer to similar elements throughout the figures.

FIG. 1 is a functional block diagram illustrating an exemplaryembodiment of a test system for electrofluidic measurement of a fluiddelivery by a fluid infusion device according to various teachings ofthe present disclosure;

FIG. 2 is a perspective view of a test housing of the test system ofFIG. 1;

FIG. 3 is a cross-sectional view of the test housing, taken along line3-3 of FIG. 2;

FIG. 4A is a dataflow diagram illustrating a test control system of thetest system of FIG. 1, in accordance with various embodiments;

FIG. 4B is a continuation of the dataflow diagram of FIG. 4A;

FIG. 5 is a dataflow diagram illustrating a test control module of thetest control system of FIGS. 4A and 4B, in accordance with variousembodiments;

FIG. 6 illustrates an exemplary bolus or bolus amount user interfacerendered by the test system on a display of a human-machine interfaceassociated with the test system of FIG. 1, in accordance with variousembodiments;

FIG. 7 illustrates an exemplary bolus error user interface rendered bythe test system on the display of the human-machine interface associatedwith the test system of FIG. 1, in accordance with various embodiments;

FIG. 8 illustrates an exemplary basal rate user interface rendered bythe test system on the display of the human-machine interface associatedwith the test system of FIG. 1, in accordance with various embodiments;

FIG. 9 illustrates an exemplary basal error user interface rendered bythe test system on the display of the human-machine interface associatedwith the test system of FIG. 1, in accordance with various embodiments;

FIG. 10 is a flowchart illustrating a control method for the test systemof FIG. 1, in accordance with various embodiments;

FIG. 11 is a flowchart illustrating a calibration control method for thetest system of FIG. 1, in accordance with various embodiments;

FIG. 12 is a flowchart illustrating a bolus test control method for thetest system of FIG. 1, in accordance with various embodiments; and

FIG. 13 is a flowchart illustrating a basal test control method for thetest system of FIG. 1, in accordance with various embodiments.

DETAILED DESCRIPTION

The following detailed description is merely illustrative in nature andis not intended to limit the embodiments of the subject matter or theapplication and uses of such embodiments. As used herein, the word“exemplary” means “serving as an example, instance, or illustration.”Any implementation described herein as exemplary is not necessarily tobe construed as preferred or advantageous over other implementations.Furthermore, there is no intention to be bound by any expressed orimplied theory presented in the preceding technical field, background,brief summary or the following detailed description.

Certain terminology may be used in the following description for thepurpose of reference only, and thus are not intended to be limiting. Forexample, terms such as “top”, “bottom”, “upper”, “lower”, “above”, and“below” could be used to refer to directions in the drawings to whichreference is made. Terms such as “front”, “back”, “rear”, “side”,“outboard”, and “inboard” could be used to describe the orientationand/or location of portions of the component within a consistent butarbitrary frame of reference which is made clear by reference to thetext and the associated drawings describing the component underdiscussion. Such terminology may include the words specificallymentioned above, derivatives thereof, and words of similar import.Similarly, the terms “first”, “second”, and other such numerical termsreferring to structures do not imply a sequence or order unless clearlyindicated by the context.

As used herein, the term “axial” refers to a direction that is generallyparallel to or coincident with an axis of rotation, axis of symmetry, orcenterline of a component or components. For example, in a cylinder ordisc with a centerline and generally circular ends or opposing faces,the “axial” direction may refer to the direction that generally extendsin parallel to the centerline between the opposite ends or faces. Incertain instances, the term “axial” may be utilized with respect tocomponents that are not cylindrical (or otherwise radially symmetric).For example, the “axial” direction for a rectangular housing containinga rotating shaft may be viewed as a direction that is generally parallelto or coincident with the rotational axis of the shaft. Furthermore, theterm “radially” as used herein may refer to a direction or arelationship of components with respect to a line extending outward froma shared centerline, axis, or similar reference, for example in a planeof a cylinder or disc that is perpendicular to the centerline or axis.In certain instances, components may be viewed as “radially” alignedeven though one or both of the components may not be cylindrical (orotherwise radially symmetric). Furthermore, the terms “axial” and“radial” (and any derivatives) may encompass directional relationshipsthat are other than precisely aligned with (e.g., oblique to) the trueaxial and radial dimensions, provided the relationship is predominatelyin the respective nominal axial or radial direction. As used herein, theterm “transverse” denotes an axis that crosses another axis at an anglesuch that the axis and the other axis are neither substantiallyperpendicular nor substantially parallel.

As used herein, the term module refers to any hardware, software,firmware, electronic control component, processing logic, and/orprocessor device, individually or in any combination, including withoutlimitation: application specific integrated circuit (ASIC), anelectronic circuit, a processor (shared, dedicated, or group) and memorythat executes one or more software or firmware programs, a combinationallogic circuit, and/or other suitable components that provide thedescribed functionality.

Embodiments of the present disclosure may be described herein in termsof schematic, functional and/or logical block components and variousprocessing steps. It should be appreciated that such block componentsmay be realized by any number of hardware, software, and/or firmwarecomponents configured to perform the specified functions. For example,an embodiment of the present disclosure may employ various integratedcircuit components, e.g., memory elements, digital signal processingelements, logic elements, look-up tables, or the like, which may carryout a variety of functions under the control of one or moremicroprocessors or other control devices. In addition, those skilled inthe art will appreciate that embodiments of the present disclosure maybe practiced in conjunction with any number of systems, and that thetest systems described herein is merely exemplary embodiments of thepresent disclosure.

For the sake of brevity, conventional techniques related to signalprocessing, data transmission, signaling, control, and other functionalaspects of the systems (and the individual operating components of thesystems) may not be described in detail herein. Furthermore, theconnecting lines shown in the various figures contained herein areintended to represent example functional relationships and/or physicalcouplings between the various elements. It should be noted that manyalternative or additional functional relationships or physicalconnections may be present in an embodiment of the present disclosure.

The following description relates to various embodiments of a testsystem for measuring an amount of fluid delivered by a fluid infusiondevice to determine an accuracy of the fluid infusion device. The testsystem is a closed system, which is resistant to environmental factors,including temperature of the testing environment, evaporation,vibrations, humidity and air density. The test system provides a userinterface to measure an amount of fluid dispensed by a variety of fluidinfusion devices to determine a fluid delivery accuracy for the varietyof fluid infusion devices, such as insulin infusion devices. The testsystem further enables precise and accurate measurement of the smallamounts of fluid dispensed by the insulin infusion devices, includingprecise and accurate measurements for nanoliters and microlitersdispensed by the insulin infusion devices, which may be used todetermine an accuracy of the insulin infusion devices. It should benoted that while the test system is described herein as being used withan insulin infusion device, such as an insulin infusion pump, it will beunderstood that the test system may be employed with a variety of otherfluid infusion devices and/or medical devices. Thus, while thenon-limiting examples described below relate to a test system for usewith a fluid infusion device used to treat diabetes, embodiments of thedisclosed subject matter are not so limited.

With reference to FIG. 1, a functional block diagram of a test system100 for measuring an amount of fluid delivered by a fluid infusiondevice 102 is shown. In this example, the test system 100 includes thefluid infusion device 102, an infusion set 104, a fluid delivery testdevice 106, an input device 108, a display 110, a power source 112 and acontroller 114. The input device 108 and the display 110 are part of ahuman-machine interface 116. The human-machine interface 116 and thecontroller 114 may be associated with a computing device, such as adesktop computer, laptop computer, tablet or other computing devicecapable of receiving input, displaying output and controlling the fluiddelivery test device 106. Generally, the test system 100 measures anamount of fluid dispensed by the fluid infusion device 102, compares themeasured amount of fluid dispensed to the amount of fluid commanded tobe dispensed by the fluid infusion device 102 and determines, based onthe comparison, whether the amount of fluid delivered by the fluidinfusion device 102 is accurate. In other embodiments, the test system100 may be used to calibrate the fluid infusion device 102.

The fluid infusion device 102 dispenses a volume of a fluid 118 to thefluid delivery test device 106 through the infusion set 104. In oneexample, the fluid infusion device 102 is an insulin infusion device,such as an insulin infusion pump. As the fluid infusion device 102comprises any suitable fluid infusion device known in the art, the fluidinfusion device 102 will not be discussed in great detail herein. Forexample, the fluid infusion device 102 can comprise an insulin infusiondevice, such as the MiniMed™ 670G Insulin Pump System, the MiniMedParadigm® REAL-Time Revel™ Insulin Pump, MiniMed™ 630G Insulin PumpSystem, MiniMed™ 530G Insulin Pump, MiniMed™ 640G Insulin Pump Systemeach offered for sale by Medtronic MiniMed, Inc. of Northridge, Calif.Briefly, the fluid infusion device 102 is designed to be carried or wornby the patient. The fluid infusion device 102 may leverage a number ofconventional features, components, elements, and characteristicsdescribed in U.S. Pat. Nos. 6,485,465 and 7,621,893, the relevantcontent of which is incorporated by reference herein. In addition, thefluid infusion device 102 may comprise the fluid infusion devicedescribed in U.S. Publication No. 2014/0207065, which is incorporated byreference herein.

Generally, the fluid infusion device 102 includes a fluid reservoir 120,which contains the fluid 118. Depending upon the particular fluidinfusion device 102, the fluid reservoir 120 may be removably coupled tothe fluid infusion device 102 or may be fixedly disposed within thefluid infusion device 102. In one example, the fluid reservoir 120 cancomprise the fluid reservoir described in U.S. Publication No.2014/0207065, which is incorporated by reference herein. It should beunderstood, however, that the fluid reservoir 120 can comprise anysuitable fluid reservoir 120 that is capable of receiving and/ordispensing a fluid, and thus, the fluid reservoir 120 is merely anexample. Generally, the fluid reservoir 120 is pre-filled with the fluid118 prior to initiating a test, and the fluid infusion device 102 isprimed prior to initiating the test.

In one example, the fluid 118 is an electrically conductive liquid. Thefluid 118 is an electrolytic solution that has fluid properties that maybe generally analogous to the fluid properties of insulin, for example,the fluid 118 is Newtonian and the surface energy of the fluid wheninterfacing with air is not greater than that of water interfacing withair. In this example, the fluid 118 is a potassium chloride (KCl)solution. It should be noted that any number of electrolytic solutionsmay be used for the fluid 118, including, but not limited to, a solutioncontaining ammonium sulfate, calcium chloride, sodium chloride,potassium carbonate, sodium phosphate or other salt. In the example ofthe fluid 118 as comprising the potassium chloride solution, the fluid118 has a concentration of about 2.5% by mass potassium chloride, whichhas a conductivity of about 29.5 millisiemens per centimeter (mS/cm). Inone example, the fluid 118 may be employed in a test environment havinga temperature of about 20 degrees Celsius (° C.).

The fluid infusion device 102 is controllable by an operator to dispensethe fluid 118 from the fluid reservoir 120 in increments to perform thetest. In one example, the operator or user controls the fluid infusiondevice 102, via a human-machine interface of the fluid infusion device102, to dispense the fluid 118 from the fluid reservoir 120. As isgenerally known, the fluid infusion device 102 includes one or moreinput devices, which enable the operator to select an amount of thefluid 118 to be dispensed from the fluid reservoir 120 by the fluidinfusion device 102. For example, the operator may select to dispensethe fluid 118 in increments or boluses of a pre-defined discrete volumeor at a volume of fluid for a particular period of time (basal rate).For example, a pre-defined volume for a bolus may be about 250nanoliters (nL). The amount of the fluid 118 selected to be dispensed bythe operator of the fluid infusion device 102 may be input to thecontroller 114 via the human-machine interface 116. In one example, foreach command input by the operator to the fluid infusion device 102 todispense an increment of the fluid 118, the operator may input thecommanded increment via the human-machine interface 116 to thecontroller 114. In certain embodiments, the controller 114 maycommunicate directly with the fluid infusion device 102, over a suitablewireless communication protocol, and may command the fluid infusiondevice 102 to dispense the fluid 118 at a particular increment.

The infusion set 104 is fluidly coupled to the fluid reservoir 120 ofthe fluid infusion device 102. As the infusion set 104 comprises anysuitable fluid infusion set known in the art, the infusion set 104 willnot be discussed in great detail herein. For example, the infusion set104 can comprise an insulin infusion set, such as the MiniMed Quick-set®infusion set offered for sale by Medtronic MiniMed, Inc. of Northridge,Calif. In one example, the infusion set 104 includes a flexible tubingor conduit 122, which is coupled at one end to a set connector 124 andis coupled at an opposite end to an infusion unit 126. The set connector124 defines a fluid flow path for the fluid 118 from the fluid reservoir120. The infusion unit 126 is fluidly coupled to the conduit 122 at adistal end of the conduit 122 and provides a fluid pathway from thefluid reservoir 120 to the body of the patient. The infusion unit 126generally includes a fluid outlet or cannula 128. In this example, thecannula 128 is fluidly coupled to the fluid delivery test device 106 todeliver the fluid 118 from the fluid reservoir 120 to the fluid deliverytest device 106.

The fluid delivery test device 106 is in fluid communication with thefluid reservoir 120 to receive the fluid 118 via the infusion set 104.Stated another way, the fluid delivery test device 106 receives thefluid 118 from the fluid infusion device 102, which is communicatedthrough the fluid flow path defined by the infusion set 104. The fluiddelivery test device 106 is also in communication with the controller114 and the power source 112. In one example, the fluid delivery testdevice 106 includes a test housing 130, a plurality of input electrodes132 and a plurality of output electrodes 134.

With reference to FIG. 2, the test housing 130 is shown with the inputelectrodes 132 and the output electrodes 134 removed for clarity. Asshown in FIG. 2, the test housing 130 is integrally formed, monolithicor one-piece. The test housing 130 may be composed of a non-conductivematerial. In this example, the test housing 130 is composed of apolymer-based material, including, but not limited to, Polyjet VeroClearmaterial. The test housing 130 may be formed through 3D printing orother additive manufacturing techniques, or may be machined, cast,molded, etc. The test housing 130 includes a first housing end 140opposite a second housing end 142, a first housing side 144 opposite asecond housing side 146, a first housing surface 148 opposite a secondhousing surface 150 and an internal channel 152.

In one example, the first housing end 140 is stepped, and includes aprojection 154. It should be noted, however, that the first housing end140 may be substantially planar or flat. In this example, the projection154 defines a cleaning inlet 156. The cleaning inlet 156 is defined on asurface 154 a of the projection 154. The cleaning inlet 156 is in fluidcommunication with an inlet 158 of the internal channel 152. Thecleaning inlet 156 enables the internal channel 152 to be cleaned orprepared for another test. For example, a cleaning fluid, such ascompressed air or a liquid cleaning solution may be used to remove thefluid 118 (FIG. 1) from the test housing 130.

The second housing end 142 is substantially flat or planar, and definesan outlet port 160. The outlet port 160 is in fluid communication withthe internal channel 152, and enables the fluid 118 and the cleaningfluid, to exit the internal channel 152 and the test housing 130.

The first housing side 144 interconnects the first housing end 140 andthe second housing end 142. The first housing side 144 defines aplurality of input electrode bores 162. In one example, the firsthousing side 144 defines about 10 input electrode bores 162 a-162 j. Itshould be noted; however, that the first housing side 144 can define anynumber of input electrode bores 162 a . . . 162 n. Each of the inputelectrode bores 162 a-162 j receives a respective one of the pluralityof input electrodes 132. In this example, each of the input electrodebores 162 a-162 j is circular or cylindrical, and is in communicationwith the internal channel 152. Each of the input electrodes 132 a-132 jare spaced a predetermined distance D apart, and thus, each of the inputelectrode bores 162 a-162 j are also spaced a predetermined distanceapart to accommodate the distance D between each of the input electrodes132 a-132 j. In one example, in order to determine the distance Dbetween each of the input electrodes 132 a-132 j, the following equationis used:

$\begin{matrix}{\left( {D \pm x_{2}} \right) = {\frac{v_{m}}{\left( {A_{c} \pm x_{1}} \right)} - W_{e}}} & (1)\end{matrix}$

Wherein, A_(c) is the cross-sectional area of the internal channel 152in millimeters (mm); x₁ is the manufacturing tolerance associated withthe cross-sectional area of the internal channel 152, which in oneexample, is a manufacturing tolerance associated with the width and theheight of the internal channel 152 (in the example of a cylindricalinternal channel 152, x₁ is the manufacturing tolerance associated withthe radius (R_(c)) of the internal channel 152); x₂ is the manufacturingtolerance associated with the spacing between each of the inputelectrodes 132 a-132 j and each of the output electrodes 134 a-134 j,respectively; W_(e) is the thickness of the input electrodes 132 a-132 jand the output electrodes 134 a-134 j in millimeters (mm), which in thisexample is the same; V_(m) is the minimum resolution of fluid volumethat is desired to be measured or observed by the output electrode 134a-134 j of the test system 100 in microliters (μL); and D is thedistance between each of the input electrodes 132 a-132 j and each ofoutput electrodes 134 a-134 j, respectively, of the test housing 130(measured between respective ends 174 a-174 j; 176 a-176 j) inmillimeters (mm), which in this example is the same. In one example, thedistance D is about 2.86 millimeters (mm) to about 3.49 millimeters(mm), based on a radius R_(c) (FIG. 3) of the internal channel 152 ofabout 0.87 millimeters (mm) to about 1.06 millimeters (mm) and a desiredmeasured volume V_(m) of 10 microliters (μL). In one example, thedistance D is greater than the radius R_(c); however, in other examples,the distance D may be equal to or less than the radius R_(c). In otherexamples, the first housing side 144 need not include the plurality ofinput electrode bores 162, rather, wiring for the plurality of inputelectrodes 132 may be internal to or contained within the test housing130. Based on the distance D and the known thickness W_(e) of the inputelectrodes 132 a-132 j, each of the input electrode bores 162 a-162 jare defined a predetermined distance apart to ensure the distance Dbetween each of the input electrodes 132 a-132 j is maintained.

The second housing side 146 interconnects the first housing end 140 andthe second housing end 142. The second housing side 146 defines aplurality of output electrode bores 164. In one example, the secondhousing side 146 defines about 10 output electrode bores 164 a-164 j. Itshould be noted; however, that the second housing side 146 can defineany number of output electrode bores 164 a . . . 164 n. Each of theoutput electrode bores 164 a-164 j receives a respective one of theplurality of output electrodes 134. In this example, each of the outputelectrode bores 164 a-164 j is circular or cylindrical, and is incommunication with the internal channel 152. In other examples, thesecond housing side 146 need not include the plurality of outputelectrode bores 164, rather, wiring for the plurality of outputelectrodes 134 may be internal to or contained within the test housing130.

Each of the output electrode bores 164 a-164 j is associated with arespective one of the input electrode bores 162 a-162 j and each of theoutput electrode bores 164 a-164 j is also spaced the predetermineddistance apart to accommodate the spacing of the output electrodes 134a-134 j the predetermined distance D apart. Based on the distance D andthe known thickness W_(e) of the output electrodes 134 a-134 j, each ofthe output electrode bores 164 a-164 j are defined a predetermineddistance apart to ensure the distance D between each of the outputelectrodes 134 a-134 j is maintained. As will be discussed, by spacingeach of the input electrodes 132 a-132 j and each of the outputelectrodes 134 a-134 j, respectively, apart by the predetermineddistance D, an amount or volume of the fluid 118 dispensed by the fluidinfusion device 102 may be determined by the controller 114. Generally,each of the output electrode bores 164 a-164 j is offset from arespective one of the input electrode bores 162 a-162 j. In this regard,in this example, the input electrode bores 162 a-162 j are defined suchthat each one of the input electrode bores 162 a-162 j is definedbetween a respective pair of the output electrode bores 164 a-164 j.Generally, each input electrode bore 162 a-162 j is defined halfwaybetween adjacent ones of the plurality of output electrode bores 164a-164 j, which doubles a resolution of a signal received from theplurality of output electrodes 134. In this example, the plurality ofinput electrode bores 162 a-162 j and the plurality of output electrodebores 164 a-164 j are defined in the test housing 130 so as to be nearor proximate the second housing end 142.

The first housing surface 148 interconnects the first housing side 144and the second housing side 146; and interconnects the first housing end140 and the second housing end 142. The first housing surface 148 issubstantially planar or flat, and defines an infusion set inlet port166. In this example, the infusion set inlet port 166 is defined near orproximate the first housing end 140. The infusion set inlet port 166 issized and configured to receive the cannula 128. In one example, theinfusion set inlet port 166 is substantially cylindrical, and is sizedto have a clearance fit with the cannula 128. It should be noted that inother embodiments, the infusion set inlet port 166 may include a septumor have an interference fit with the cannula 128 to provide a fluid sealbetween the cannula 128 and the test housing 130, which inhibits fluid,such as air, from entering the test housing 130. In one example, theinfusion set inlet port 166 has a diameter D3 of about 1.27 millimeters(mm) and a length L2 of about 9.0 millimeters (mm).

The infusion set inlet port 166 is in fluid communication with theinternal channel 152 to provide a fluid flow path from the fluidinfusion device 102 via the infusion set 104 into the test housing 130.As will be discussed, the fluid 118 received from the cannula 128 of theinfusion set 104 flows into the internal channel 152 to determine anamount of the fluid 118 or a volume of the fluid 118 dispensed by thefluid infusion device 102. The infusion set inlet port 166 is generallydefined through the first housing surface 148 so as to be spaced adistance D2 apart from the input electrode bore 162 a and the outputelectrode bore 164 a. In one example, the distance D2 is about 1.5millimeters to about 3.5 millimeters (mm), which provides a bufferbefore the fluid 118 contacts the plurality of input electrodes 132 andthe plurality of output electrodes 134. The distance D2 also serves as apriming distance, which enables the fluid infusion device 102 and thetest housing 130 to be primed with the fluid 118 prior to the startingof a test. The infusion set inlet port 166 is also defined so as toextend along an axis A, which is substantially perpendicular to alongitudinal axis L of the test housing 130. The first housing surface148 also provides a surface for positioning or resting the infusion set104 on the test housing 130. The second housing surface 150interconnects the first housing side 144 and the second housing side146; and interconnects the first housing end 140 and the second housingend 142. The second housing surface 150 is substantially planar or flat.

The internal channel 152 is defined through the test housing 130 fromthe first housing end 140 to the second housing end 142. In one example,the internal channel 152 is defined so as to extend along linearly alongthe longitudinal axis L of the test housing 130. The internal channel152 extends from a first channel end 170 to a second channel end 172.The first channel end 170 is in fluid communication with the cleaninginlet 156, and the second channel end 172 is in fluid communication withthe outlet port 160. The internal channel 152 is also in fluidcommunication with the infusion set inlet port 166, each of theplurality of input electrode bores 162 a-162 j and each of the pluralityof output electrode bores 164 a-164 j. Generally, with reference to FIG.3, the internal channel 152 is cylindrical. The plurality of inputelectrode bores 162 a-162 j and the plurality of output electrode bores164 a-164 j intersect a diameter of the internal channel 152 and arepositioned on opposite sides of the internal channel 152. In oneexample, the internal channel 152 has a length L3, which is sized toenable a predetermined number of volume measurements of the fluid 118.In this example, the internal channel 152 has a length L3 of about 31.2millimeters (mm) to about 32.2 millimeters (mm), which enables about 10measurements of about 0.01 milliliters (mL) (10 microliters (μL)).Generally, the fluid 118 is received in the internal channel 152 suchthat in order for the fluid 118 to move along the internal channel 152,additional fluid 118 must be received through the infusion set inletport 166. Thus, each of the input and output electrodes 132 a, 134 a;132 b, 134 b . . . 132 j, 134 j is capable of measuring a discretevolume of fluid received through the infusion set inlet port 166. Incertain embodiments, the internal channel 152 may be defined as adiscrete component, which is positioned within the test housing 130instead of being monolithically, integrally formed with or integrallydefined within the test housing 130. For example, depending upon thesize of the measurements required by the test housing 130, the internalchannel 152 may be etched onto a glass substrate and coated with ahydrophobic finish. The glass substrate comprising the internal channel152 may then be coupled within the test housing 130, via adhesives,ultrasonic welding, mechanical fasteners, etc.

With reference back to FIG. 1, each of the plurality of input electrodes132 receives current at a particular voltage from the power source 112,and each of the plurality of input electrodes 132 is in communicationwith the power source 112 to receive the current at the particularvoltage. In one example, the input voltage is about 1.0 volts (V). Itshould be noted, however, that another suitable voltage may be used. Inthis example, the plurality of input electrodes 132 include 10 inputelectrodes 132 a-132 j, which are received in a respective one of theinput electrode bores 162 a-162 j. It should be noted that the fluiddelivery test device 106 may include any number of input electrodes 132a . . . 132 n, and a corresponding number of input electrode bores 162 a. . . 162 n. In this example, each of the input electrodes 132 a-132 jcomprises conductive wire. In one example, each of the input electrodes132 a-132 j comprise 30 gauge electrical wire, with one end of the inputelectrode 132 a-132 j received in a respective one of the inputelectrode bores 162 a-162 j, and the opposite end of the input electrode132 a-132 j coupled to and in communication with the power source 112 toreceive the input current at the particular voltage. In one example, athickness W_(e) of each of the input electrodes 132 a-132 j is about0.24 millimeters (mm) to about 0.26 millimeters (mm). With reference toFIG. 3, an end 174 a of the input electrode 132 a is shown receivedwithin the internal channel 152. Generally, for each of the inputelectrodes 132 a-132 j, the end 174 a-174 j is received within theinternal channel 152 so as to be in contact with and in fluidcommunication with the fluid 118 received within the internal channel152. It should be noted that the input electrodes 132 a-132 j need notcomprise electrical wire, but rather, any suitable electrode may beemployed, including, but not limited to, flat panel electrodes. In theexample of flat panel input electrodes, the flat panel input electrodesmay be coupled to sidewalls of the internal channel 152.

Each of the plurality of output electrodes 134 receive as input thecurrent applied to the respective one of the input electrodes 132 a-132j as conducted by the fluid 118 within the internal channel 152. Each ofthe plurality of output electrodes 134 is in communication with thecontroller 114 and outputs a signal based on current received from therespective input electrodes 132 a-132 j through the fluid 118. Statedanother way, each of the output electrodes 134 is in communication withthe fluid 118 to receive the current applied to the respective inputelectrode 132 a-132 j through the fluid 118, and to transmit a signal tothe controller 114 that the current has been received. In other words, apair of electrodes that comprises an input electrode 132 a-132 j and anoutput electrode 134 a-134 j is spaced apart by the internal channel 152that forms an open switch. In this example, the output electrodes 134a-134 j are connected to ground. When the fluid 118 is received withinthe internal channel 152 and is in communication with the respectiveinput electrode 132 a-132 j and the respective one or more outputelectrodes 134 a-134 j, the fluid 118 closes the switch, allowing thecurrent applied to the respective input electrode 132 a-132 j totransfer through the fluid 118 to the respective one or more outputelectrodes 134 a-134 j, which results in a current reading or signalbeing communicated to the controller 114. Thus, an open circuit (airbetween the input electrodes 132 a-132 j and the output electrodes 134a-134 j) yields a signal of zero, and a closed circuit (electrolyticfluid between the input electrodes 132 a-132 j and the output electrodes134 a-134 j) yields a signal of about 1.0 volt (V) and indicates thatthe fluid 118 has reached a particular output electrode 134 a-134 j.

In this example, the plurality of output electrodes 134 include 10output electrodes 134 a-134 j, which are received in a respective one ofthe output electrode bores 164 a-164 j. It should be noted that thefluid delivery test device 106 may include any number of outputelectrodes 134 a . . . 134 n that correspond to a respective number ofinput electrodes 132 a . . . 132 n, and a corresponding number of outputelectrode bores 162 a . . . 162 n. In this example, each of the outputelectrodes 134 a-134 j comprises conductive wire. In one example, eachof the output electrodes 134 a-134 j comprise 30 gauge electrical wire,with one end of the output electrodes 134 a-134 j received in arespective one of the output electrode bores 164 a-164 j, and theopposite end of the output electrodes 134 a-134 j coupled to and incommunication with the controller 114 to provide the controller 114 witha signal or the current received. In this example, each of the outputelectrodes 134 a-134 j is associated with a respective input port of thecontroller 114 such that the controller 114 is able to identify theparticular output electrode 134 a-134 j the current or signal isreceived from. Generally, a thickness W_(e) of each of the outputelectrodes 134 a-134 j is the same as the W_(e) of each of the inputelectrodes 132 a-132 j, and in this example, is about 0.24 millimeters(mm) to about 0.26 millimeters (mm). It should be noted that the outputelectrodes 134 a-134 j need not comprise electrical wire, but rather,any suitable electrode may be employed, including, but not limited to,flat panel electrodes. In the example of flat panel output electrodes,the flat panel output electrodes may be coupled to sidewalls of theinternal channel 152.

With reference to FIG. 3, an end 176 a of the output electrode 134 a isshown received within the internal channel 152. Generally, for each ofthe output electrodes 134 a-134 j, the end 176 a-176 j is receivedwithin the internal channel 152 so as to be in contact with and in fluidcommunication with the fluid 118 received within the internal channel152. In this example, the end 176 a-176 j of the respective outputelectrode 134 a-134 j is spaced apart from the end 174 a-174 j of therespective input electrode 132 a-132 j such that a gap is definedbetween the respective end 174 a-174 j and end 176 a-176 j when thefluid 118 is not disposed between or is devoid from being between therespective input and output electrodes 132 a-132 j; 134 a-134 j withinthe internal channel 152. The gap prevents or inhibits a flow of currentfrom the respective input electrode 132 a-132 j to the respective one ormore output electrodes 134 a-134 j. In this example, the gap is filledwith air; however, another electrically insulating medium that ishydrophobic may be used.

With reference back to FIG. 1, the input device 108 and the display 110form the human-machine interface 116. Each of the input device 108 andthe display 110 are in communication with the controller 114 via asuitable communication medium, such as a bus. The input device 108 maybe configured in a variety of ways. In some embodiments, the inputdevice 108 may include various switches or levers, one or more buttons,a touchscreen interface that may be overlaid on the display 110, akeyboard, an audible device, a microphone associated with a speechrecognition system, or various other human-machine interface devices.

The display 110 comprises any suitable technology for displayinginformation, including, but not limited to, a liquid crystal display(LCD), organic light emitting diode (OLED), plasma, or a cathode raytube (CRT). In this example, the display 110 is an electronic displaycapable of graphically displaying one or more user interfaces under thecontrol of the controller 114. Those skilled in the art may realizeother techniques to implement the display 110 in the test system 100.

The power source 112 is in communication with the controller 114, over asuitable communication medium, such as a bus. The power source 112provides a current at a particular voltage to the input electrodes 132a-132 j. Generally, the power source 112 creates a voltage potentialbetween the input electrodes 132 a-132 j and the output electrodes 134a-134 j (as the output electrodes 134 a-134 j are tied to ground) whenthe fluid 118 is present, which causes current to flow between therespective input electrode 132 a-132 j and the respective outputelectrode 134 a-134 j in the internal channel 152. In one example, thepower source 112 includes a direct current (DC) source. In this example,the power source 112 outputs a 5 volt (V) pulse width modulation wave,which is reduced to the about 1 volt (V) input voltage with a voltagedivider. Alternatively, an H-bridge may also be employed to invert thepulse width modulation wave to increase the input voltage, if desired.In one example, the voltage divider includes two resistors, with onehaving a resistance of about 3.3 M ohms and the other resistor having aresistance of 1.0 M ohms. In one example, the pulse width is about 0.01%and the frequency is about 5 Hertz (Hz), which reduces clustering of theions in the fluid 118 about the respective output electrode 134 a-134 j.Generally, the power source 112 applies the voltage to each of the inputelectrodes 132 a-132 j to create a voltage potential between the inputelectrodes 132 a-132 j and the output electrodes 134 a-134 j in analternating pattern to enable the ions in the fluid 118 to “reset” andprevent clustering of the electrolytes in the fluid 118 onto the outputelectrode 134 a-134 j, which inhibits the flow of the fluid 118. Thisenables the current to flow through the fluid 118 for a longer period oftime. In one example, the power source 112 applies the input voltage tothe input electrode 132 a and establishes a voltage potential betweenthe input electrode 132 a and the output electrode 134 a, then the powersource 112 applies the input voltage to the input electrode 132 b andestablishes a voltage potential between the input electrode 132 b andthe output electrode 134 b, etc., until the input voltage has beenapplied to the input electrode 132 j and establishes a voltage potentialbetween the input electrode 132 j and the output electrode 134 j; andthen the power source 112 returns to apply the input voltage to theinput electrode 132 a. Thus, the power source 112 is configured to applythe voltage to a respective one of the input electrodes 132 a-132 j in asequential pattern; however, it will be understood that the power source112 may apply the voltage to the input electrodes 132 a-132 j in anypattern that reduces the clustering of the ions of the fluid 118 aboutthe output electrodes 134 a-134 j.

Generally, the output electrodes 134 a-134 j read a voltage of either 0volts (V) or approximately 1.0 volts (V) depending on whether current isflowing through them. In this example, this signal from the outputelectrodes 134 a-134 j requires amplification since the cutoff forreading digital HIGH by at least one processor 180 of the controller 114is 3.3V. In order to amplify this signal, in this example, the outputelectrodes 134 a-134 j are each electrically connected to standardOperational Amplifier voltage comparator circuits, such as, for exampleOperational Amplifier OPA2336, which is commercially available fromTexas Instruments, Inc. of Dallas, Tex. The signal of each of the outputelectrodes 134 a-134 j is compared to a reference voltage of 0.5 volt(V). If the voltage from the output electrodes 134 a-134 j exceeds thereference voltage, the Operational Amplifier outputs a digital HIGH, andprocessor 180 determines that the fluid 118 is at the site of thatparticular output electrode 134 a-134 j in the internal channel 152.

Generally, the distance D between each of the input electrodes 132 a-132j and each of the output electrodes 134 a-134 j combined with thedimensions of the internal channel 152 provide the minimum resolution ofthis test system 100. In this example, the input electrodes 132 a-132 j,the output electrodes 134 a-134 j and their spacing are analogous thegraduations on a ruler. The number of graduations (the input electrodes132 a-132 j and the output electrodes 134 a-134 j) and the distance Deach of the input electrodes 132 a-132 j and each of the outputelectrodes 134 a-134 j are spaced apart from another, respectively,generally dictates how small or large an amount may be measured. Forexample, in order to measure 1.0 microliters (μL), the test system 100would include ten graduations or ten input electrodes 132 a-132 j andten output electrodes 134 a-134 j that are each able to measure 0.1microliter (μL).

The controller 114 includes the processor 180 and a computer readablestorage device or media 182. The processor 180 can be any custom made orcommercially available processor, a central processing unit (CPU), agraphics processing unit (GPU), an auxiliary processor among severalprocessors associated with the controller 114, a semiconductor basedmicroprocessor (in the form of a microchip or chip set), amacroprocessor, any combination thereof, or generally any device forexecuting instructions. The computer readable storage device or media182 may include volatile and nonvolatile storage in read-only memory(ROM), random-access memory (RAM), and keep-alive memory (KAM), forexample. KAM is a persistent or non-volatile memory that may be used tostore various operating variables while the processor 180 is powereddown. The computer-readable storage device or media 182 may beimplemented using any of a number of known memory devices such as PROMs(programmable read-only memory), EPROMs (electrically PROM), EEPROMs(electrically erasable PROM), flash memory, or any other electric,magnetic, optical, or combination memory devices capable of storingdata, some of which represent executable instructions, used by thecontroller 114 in controlling components associated with the test system100.

The instructions may include one or more separate programs, each ofwhich comprises an ordered listing of executable instructions forimplementing logical functions. The instructions, when executed by theprocessor 180, receive and process input signals, perform logic,calculations, methods and/or algorithms for controlling the componentsof the test system 100, and generate control signals to components ofthe test system 100 to determine an amount of the fluid 118 dispensed bythe fluid infusion device 102 based on the logic, calculations, methods,and/or algorithms. Although only one controller 114 is shown in FIG. 1,embodiments of the test system 100 can include any number of controllers114 that communicate over any suitable communication medium or acombination of communication mediums and that cooperate to process thesensor signals, perform logic, calculations, methods, and/or algorithms,and generate control signals to control features of the test system 100.

In various embodiments, one or more instructions of the controller 114are associated with the test system 100 and, when executed by theprocessor 180, the instructions receive and process signals from thehuman-machine interface 116 to test the accuracy of the fluid infusiondevice 102. For example, as will be discussed herein, the instructionsof the controller 114, when executed by the processor 180, determinewhether to perform a bolus test, a basal test or to calibrate the testhousing 130. In various embodiments, the instructions of the controller114 determine an amount of the fluid 118 or volume of the fluid 118dispensed by the fluid infusion device 102, and output one or more userinterfaces for display on the display 54 of the human-machine interface116 that illustrate the volume of the fluid 118 dispensed by the fluidinfusion device 102 over time. In various embodiments, the instructionsof the controller 114 determine the output electrode 134 a-134 jactivated by the fluid dispensed by the fluid infusion device 102, andoutput one or more user interfaces for display on the display 54 of thehuman-machine interface 116 that illustrate the number of outputelectrodes 134 a-134 j activated by the fluid over time.

Generally, prior to performing a test using the test housing 130, thefluid reservoir 120 of the fluid infusion device 102 is pre-filled withthe fluid 118, and the fluid reservoir 120 is coupled to the fluidinfusion device 102. The infusion set 104 is coupled to the fluidreservoir 120, and generally, the fluid infusion device 102, to define afluid flow path from the fluid reservoir 120. The infusion unit 126 iscoupled to the first housing surface 148 of the test housing 130 suchthat the cannula 128 is received within and coupled to the infusion setinlet port 166. With the fluid infusion device 102 fluidly coupled tothe test housing 130, the user may initiate a test of the deliveryvolume accuracy of fluid infusion device 102 and/or may initiate acalibration test to calibrate the test housing 130. In one example, thefluid infusion device 102 is primed with the fluid 118, and the testhousing 130 is also at least partially primed with the fluid 118 priorto the calibration test or the test of the delivery volume accuracy.

For example, as shown in more detail with regard to FIGS. 4 and 5, andwith continued reference to FIG. 1, dataflow diagrams illustrate variousembodiments of a test control system 200 of the test system 100, whichmay be embedded within the controller 114. Various embodiments of thetest control system 200 according to the present disclosure can includeany number of sub-modules embedded within the controller 114. As can beappreciated, the sub-modules shown in FIGS. 4 and 5 may be combinedand/or further partitioned to similarly control the input electrodes 132a-132 j and determine an amount of fluid dispensed by the fluid infusiondevice 102 based on the activated output electrode 134 a-134 j. Inputsto the test control system 200 may be received from the human-machineinterface 116 (FIG. 1), received from the output electrodes 134 a-134 j(FIG. 1), received from other control modules (not shown) associatedwith the test system 100, and/or determined/modeled by other sub-modules(not shown) within the controller 114. In various embodiments, withreference to FIGS. 4A and 4B, the test control system 200 includes auser interface (UI) control module 202, a calibration datastore 204, acalibration control module 206 and a test control module 208.

The user interface (UI) control module 202 receives input data 210. Theinput data 210 is received from a user's interaction with thehuman-machine interface 116 (FIG. 1). In one example, the input data 210comprises test type input data 212, test device input data 214, set rateinput data 216, bolus delivery data 217, fluid quantity input data 218and end test data 219. The test type input data 212 is a type of test tobe performed with the test system 100, and includes, but is not limitedto, a selection of a bolus test, a basal test and a calibration test.The test device input data 214 includes a unique identifier associatedwith a particular test housing 130; the distance D between each of theinput electrodes 132 a-132 j and each of the output electrodes 134 a-134j, respectively, of the test housing 130; the radius R_(c) of thecross-sectional area of the internal channel 152 or the cross sectionalarea A_(c) of the internal channel 152; a thickness W_(e) of the inputelectrodes 132 a-132 j and the output electrodes 134 a-134 j; amanufacturing tolerance associated with the spacing between each of theinput electrodes 132 a-132 j; a manufacturing tolerance associated withthe radius R_(c) of the cross-sectional area of the internal channel 152or a manufacturing tolerance associated with the cross-sectional areaA_(c) of the internal channel 152 (such as a manufacturing toleranceassociated with a height and a width of the internal channel 152); andthe data sampling rate associated with the output electrodes 134 a-134j. These values associated with the test device input data 214 may bepermanently coupled to the test housing 130. The test device input data214 may comprise a unique series of alpha-numeric values that areassociated with that particular test housing 130 for use with the testsystem 100, which are received as input through the human-machineinterface 116. In other embodiments, the test device input data 214 ofthe test housing 130 may comprise a scannable code, including, but notlimited to a bar code, QR code, etc., and the test device input data 214may be received as input by an optical scanning device coupled to and incommunication with the controller 114 and processed by the controller114 to determine the test device input data 214.

The set rate input data 216 is a pre-defined basal rate for the fluidthat is to be dispensed from the fluid infusion device 102 during abasal test, which may be received as input when a basal test is selectedto be performed. The basal rate is defined as a volume of fluid per unittime. The bolus delivery data 217 is optional input received from theuser via the user's manipulation of the input device 108 that indicatesthat the bolus has been delivered by the fluid infusion device 102. Thefluid quantity input data 218 is an expected or pre-defined volume offluid to be received into the test housing 130 a pre-defined number oftimes, which may be received as input during a calibration test or abolus test. In this regard, for a calibration test, pre-defined volumesof fluid may be dispensed into the test housing 130 through the infusionset inlet port 166 a predetermined number of times until the outlet port160 of the internal channel 152 is reached. In one example, acalibrated, high-precision syringe pump may provide the known orpre-defined volume of fluid for delivery into the test housing 130during a calibration test.

In a bolus test, a predetermined number of expected volumes of fluid orboluses are to be dispensed into the test housing 130 by the fluidinfusion device 102. Generally, a bolus test determines an accuracy ofthe fluid infusion device 102 to dispense a number of discrete volumesor boluses of fluid, and the fluid quantity input data 218 is apre-defined number of the discrete volumes to be dispensed into the testhousing 130 along with a pre-defined expected volume to be received fromthe fluid infusion device 102. The end test data 219 is input receivedfrom the user via the user's manipulation of the input device 108 to enda basal test.

The UI control module 202 receives and processes the test type inputdata 212 and determines whether input has been received to select abolus test, basal test or calibration test. Based on a receivedselection of a bolus test, the UI control module 202 sets bolus testcommand 220 for the test control module 208. The bolus test command 220instructs the test control module 208 to begin a bolus test. Based on areceived selection of a basal test, the UI control module 202 sets basaltest command 222 for the test control module 208. The basal test command222 instructs the test control module 208 to begin a basal test. Basedon a received selection of a calibration test, the UI control module 202sets calibration test command 224 for the calibration control module206. The calibration test command 224 instructs the calibration controlmodule 206 to begin a calibration test.

The UI control module 202 receives and processes the test device inputdata 214. Based on the test device input data 214, the UI control module202 sets test device data 226 for the calibration control module 206 andthe test control module 208. The test device data 226 is the uniqueidentifier associated with the test housing 130, the distance D betweeneach of the input electrodes 132 a-132 j and each of the outputelectrodes 134 a-134 j, respectively, of the test housing 130, theradius R_(c) of the cross-sectional area of the internal channel 152 orA_(c) the cross-sectional area of the internal channel 152, thethickness of the input electrodes 132 a-132 j, the manufacturingtolerance associated with the spacing between each of the inputelectrodes 132 a-132 j and each of the output electrodes 134 a-134 j,respectively, the manufacturing tolerance associated with the radiusR_(c) of the cross-sectional area of the internal channel 152 or amanufacturing tolerance associated with the cross-sectional area A_(c)of the internal channel 152 (such as a manufacturing toleranceassociated with a height and a width of the internal channel 152), andthe data sampling rate associated with the output electrodes 134 a-134j.

The UI control module 202 receives and processes the set rate input data216. Based on the set rate input data 216, the UI control module 202sets rate data 228 for the test control module 208. The rate data 228 isthe pre-defined basal rate for the fluid infusion device 102. The UIcontrol module 202 receives and processes the fluid quantity input data218. Based on the fluid quantity input data 218, the UI control module202 sets test fluid quantity data 230 for the calibration control module206 and the test control module 208. The test fluid quantity data 230 isthe pre-defined volume of fluid to be received into the test housing 130each of the pre-defined number of times. The UI control module 202receives and processes the bolus delivery data 217. Based on the bolusdelivery data 217, the UI control module 202 sets bolus deliveredcommand 261 for the test control module 208. The UI control module 202receives and processes the end test data 219. Based on the end test data219, the UI control module 202 sets end test command 263 for the testcontrol module 208.

The UI control module 202 also receives as input bolus amount data 232from the test control module 208. The bolus amount data 232 is a volumeof fluid received from the fluid infusion device 102 at each of thepre-defined number of times over a period of time. Based on the bolusamount data 232, the UI control module 202 generates a bolus or bolusamount user interface (UI) 234 for display on the display 110 of thehuman-machine interface 116 (FIG. 1). The bolus amount user interface234 graphically and/or textually displays the volume of fluid receivedfrom the fluid infusion device 102 at each of the pre-defined number oftimes over the period of time.

In one example, with reference to FIG. 6, an exemplary bolus amount userinterface 234 is shown. In this example, the bolus amount user interface234 is a graph, in which “Volume” in microliters (μL) is measured alonga y-axis 300, and “Time” in hours (h) is measured on an x-axis 302. Inone example, the y-axis 300 ranges from about 186.0 μL to about 186.3however, the y-axis 300 may have any desired range. The x-axis 302ranges from 0 to 0.35 hours, however, the x-axis 302 may have anydesired range. A graphical indicator 304, for example, a line, isassociated with each discrete volume of fluid received by the testhousing 130. As each volume of fluid received by the test housing 130 isdiscrete during a bolus test, the resultant graph has a plurality ofsteps or levels, with each step or level denoting a volume of fluid orbolus dispensed for a particular time frame. The steps or levels may beinterconnected, as shown, if desired.

With reference back to FIGS. 4A and 4B, the UI control module 202 alsoreceives as input bolus error data 236 from the test control module 208.The bolus error data 236 is an error calculated by the test controlmodule 208 for each bolus received from the fluid infusion device 102.Stated another way, as will be discussed, the bolus error data 236 is avalue of a difference between the test fluid quantity data 230 and thefluid received from the fluid infusion device 102 at each of thepre-defined number of times, which indicates a fluid delivery accuracyof the fluid infusion device 102.

Based on the bolus error data 236, the UI control module 202 generates abolus error user interface (UI) 238 for display on the display 110 ofthe human-machine interface 116 (FIG. 1). The bolus error user interface238 graphically and/or textually displays the error associated with eachvolume of fluid received from the fluid infusion device 102 at each ofthe pre-defined number of times.

In one example, with reference to FIG. 7, an exemplary bolus error userinterface 238 is shown. In this example, the bolus error user interface238 is a graph, in which “Percent Error” is measured along a y-axis 320,and “Bolus Number in the Test Sequence” is measured on an x-axis 322. Inone example, the y-axis 320 ranges from −10 to 25, however, the y-axis320 may have any desired range. The x-axis 322 ranges from 0 to 25,however, the x-axis 322 may have any desired range. A graphicalindicator 326, for example, a circle, is associated with each number offluid volumes received and is positioned at the error calculated forthat particular received volume of fluid. For example, graphicalindicator 326-1 is associated with the second volume of fluid receivedin the test housing 130, and has a percent error of about −6.5%;graphical indicator 326-2 is associated with the fifteenth volume offluid received in the test housing 130, and has a percent error of about11.6%. Each of the graphical indicators 326 may be interconnected with aline, which graphically illustrates the error between each bolusdispensed by the fluid infusion device 102. The bolus error userinterface 238 also includes a mean bolus error may be graphicallyindicated on the bolus error user interface 238 as a dashed line 308.The mean bolus error may be calculated by the test control module 208 asan average of the errors calculated by the test control module 208 foreach bolus received from the fluid infusion device 102. The bolus erroruser interface 238 may also include a key 328, which may be superimposedover a portion of the bolus error user interface 238. In variousembodiments, the bolus error user interface 238 may also include aserial number of the fluid infusion device 102, which may be received asinput to the UI control module 202 based on a user's interaction withthe input device 108; a date; a time; a number of boluses delivered(from the bolus amount data 232); a size or volume of each of theboluses (from the test fluid quantity data 230); and the uniqueidentifier of the test housing 130 from the test device input data 214.

With reference back to FIGS. 4A and 4B, the UI control module 202 alsoreceives as input basal rate data 240 from the test control module 208.The basal rate data 240 is a volume of fluid delivered by the fluidinfusion device 102 over a period of time. Based on the basal rate data240, the UI control module 202 generates a basal rate user interface(UI) 242 for display on the display 110 of the human-machine interface116 (FIG. 1). The basal rate user interface 242 graphically and/ortextually displays the volume of fluid delivered by the fluid infusiondevice 102 over the period of time.

In one example, with reference to FIG. 8, an exemplary basal rate userinterface 242 is shown. In this example, the basal rate user interface242 is a graph, in which “Volume” in microliters (μL) is measured alonga y-axis 340, and “Time” in hours (h) is measured on an x-axis 342. Inone example, the y-axis 340 ranges from about 186.0 μL to about 186.3however, the y-axis 340 may have any desired range. The x-axis 342ranges from 0 to 0.35 hours, however, the x-axis 342 may have anydesired range. A graphical indicator 344, for example, a line, is usedto illustrate the amount of fluid delivered by the fluid infusion device102 over the period of time.

With reference back to FIGS. 4A and 4B, the UI control module 202 alsoreceives as input basal error data 244 from the test control module 208.The basal error data 244 is an error calculated by the test controlmodule 208 for the basal rate received from the fluid infusion device102, and generally includes a maximum error value, minimum error valueand an overall error value for the dispensing of the fluid by the fluidinfusion device 102 over the period of time. Stated another way, as willbe discussed, the basal error data 244 is a maximum value, a minimumvalue and an overall value of a difference between the rate data 228 andthe rate of fluid received from the fluid infusion device 102 over theperiod of time, which indicates a fluid delivery accuracy of the fluidinfusion device 102. Based on the basal error data 244, the UI controlmodule 202 generates a basal error user interface (UI) 246 for displayon the display 110 of the human-machine interface 116 (FIG. 1). Thebasal error user interface 246 graphically and/or textually displays theerror associated with the amount of fluid received from the fluidinfusion device 102 over the period of time.

In one example, with reference to FIG. 9, an exemplary basal error userinterface 246 is shown. In this example, the basal error user interface246 is a graph, in which “Maximum, Minimum, and Overall Percent Errorfor Shotcycle Windows” is measured in percent (%) along a y-axis 360,and “Number of Shotcycles” is measured on an x-axis 362. Generally, thefluid infusion device 102 delivers fluid at data points, increments orshotcycles over the pre-defined period of time. In one example, they-axis 360 ranges from −60 to 80, however, the y-axis 360 may have anydesired range. The x-axis 362 ranges from 0 to 30, however, the x-axis362 may have any desired range. A first graphical indicator 366, forexample, a line with a plurality of raised crosses, graphicallyindicates a minimum error for the fluid infusion device 102 over thenumber of shotcycles. A second graphical indicator 368, for example, aline with a plurality of in-line crosses, graphically indicates amaximum error for the fluid infusion device 102 over the number ofshotcycles. A third graphical indicator 370, for example, a dashed line,graphically indicates an overall error for the fluid infusion device 102over the number of shotcycles. The basal error user interface 246 mayalso include a key 372, which may be superimposed over a portion of thebasal error user interface 246. In various embodiments, the basal erroruser interface 246 may also include a serial number of the fluidinfusion device 102, which may be received as input to the UI controlmodule 202 based on a user's interaction with the input device 108; adate; a time; a basal rate (from the rate data 228); and the uniqueidentifier of the test housing 130 from the test device input data 214.

With reference back to FIGS. 4A and 4B, the UI control module 202 alsoreceives as input bolus activation data 248 from the test control module208. The bolus activation data 248 is data that associates theactivation of each of the output electrodes 134 a-134 j with aparticular time and a particular volume of fluid received from the fluidinfusion device 102. Stated another way, the bolus activation data 248identifies which one of the output electrodes 134 a-134 j is activatedat a particular time by a particular one of the volumes or boluses offluid. Based on the bolus activation data 248, the UI control module 202generates a bolus activation user interface (UI) 250 for display on thedisplay 110 of the human-machine interface 116 (FIG. 1). The bolusactivation user interface 250 graphically and/or textually displays thevolume of fluid received from the fluid infusion device 102 over theperiod of time.

With to FIGS. 4A and 4B, the UI control module 202 also receives asinput basal activation data 252 from the test control module 208. Thebasal activation data 252 is data that associates the activation of eachof the output electrodes 134 a-134 j with a particular time and aparticular shotcycle of fluid received from the fluid infusion device102. Stated another way, the basal activation data 252 identifies whichone of the output electrodes 134 a-134 j is activated at a particulartime by a particular shotcycle of the fluid delivered by the fluidinfusion device 102. Based on the basal activation data 252, the UIcontrol module 202 generates a basal activation user interface (UI) 254for display on the display 110 of the human-machine interface 116 (FIG.1). The basal activation user interface 254 graphically and/or textuallydisplays the volume of fluid delivered by the fluid infusion device 102over the period of time.

Based on at least one of the bolus activation data 248 and the basalactivation data 252, the UI control module 202 also outputs data log256. The data log 256 is a text file, for example, which includes thebolus activation data 248, the basal activation data 252 or test devicecalibration data 260 in a list form. The data log 256 may also includeother characteristics associated with a bolus test or basal testperformed by the test system 100, including, but not limited to: a date;a type of test (from the test type input data 212); a unique identifierof the test housing 130 (from the test device input data 214); acalibration profile associated with the test housing 130 that was usedfor the determination of the amount of fluid dispensed by the fluidinfusion device 102 (from calibration data 258); a type of electrolyte(which may be received from the user through the input device 108 andstored in the media 182); a concentration of the electrolyte (which maybe received from the user through the input device 108 and stored in themedia 182); settings for the voltage applied to the input electrodes 132a-132 j (which may be received from the user through the input device108 and stored in the media 182); a test number (which may be receivedfrom the user through the input device 108 and stored in the media 182);a protocol number (which may be received from the user through the inputdevice 108 and stored in the media 182); a type of fluid infusion device102 (which may be received from the user through the input device 108and stored in the media 182); a serial number of the fluid infusiondevice 102 (which may be received from the user through the input device108 and stored in the media 182); a type of infusion set 104 used withthe fluid infusion device 102 (which may be received from the userthrough the input device 108 and stored in the media 182); a lot numberof the infusion set 104 (which may be received from the user through theinput device 108 and stored in the media 182); a type of test (from thetest type input data 212); a volume of fluid expected for each fluiddelivery (from the fluid quantity input data 218); a delivery frequency(which may be received from the user through the input device 108 andstored in the media 182); a total delivery amount (from the fluidquantity input data 218); a sample rate for the output electrodes 134a-134 j (which may be received from the user through the input device108 and stored in the media 182); and notes from the user (which may bereceived from the user through the input device 108 and stored in themedia 182).

The data log 256 may also include other characteristics associated witha calibration test performed by the test system 100, including, but notlimited to: a date; a unique identifier of the test housing 130 (fromthe test device input data 214); a length of the internal channel 152 ofthe test housing 130 (which may be received from the user through theinput device 108 and stored in the media 182); a height of the internalchannel 152 of the test housing 130 (which may be received from the userthrough the input device 108 and stored in the media 182); a width ofthe internal channel 152 of the test housing 130 (which may be receivedfrom the user through the input device 108 and stored in the media 182);a spacing of the input electrodes 132 a-132 j and/or the outputelectrodes 134 a-134 j (which may be received from the user through theinput device 108 and stored in the media 182); a type of electrolyte(which may be received from the user through the input device 108 andstored in the media 182); a concentration of the electrolyte (which maybe received from the user through the input device 108 and stored in themedia 182); and settings for the voltage applied to the input electrodes132 a-132 j (which may be received from the user through the inputdevice 108 and stored in the media 182). Generally, the settings for thevoltage applied to the input electrodes 132 a-132 j are pre-defined,based on the type of power source 112 employed with the test system 100(FIG. 1).

The UI control module 202 also receives as input bolus prompt 255 fromthe test control module 208. The bolus prompt 255 is a command to promptthe user to deliver another volume of fluid or a bolus to the testhousing 130 (FIG. 1). Based on the receipt of the bolus prompt 255, theUI control module 202 outputs a prompt user interface (UI) 257. Theprompt user interface 257 may be a graphical and/or textualnotification, which may be superimposed over a portion of a userinterface on the display 110, which instructs the user to dispenseanother volume of fluid or a bolus into the test housing 130 (FIG. 1).For example, the prompt user interface 257 may comprise a pop-up window,which states “Deliver Bolus” or the like.

The UI control module 202 also receives as input error flag 259 from thetest control module 208. The error flag 259 is a notification that acommunication error exists between the test housing 130 and thecontroller 114. For example, the error flag 259 indicates that one ormore of the input electrodes 132 a-132 j and/or output electrodes 134a-134 j are uncoupled from or no longer in communication with thecontroller 114. Based on the error flag 259, the UI control module 202outputs an error user interface (UI) 265. The error user interface 265may be a graphical and/or textual notification, which may besuperimposed over a portion of a user interface on the display 110,which instructs the user that a communication error exists. For example,the error user interface 265 may comprise a pop-up window, which states“Check Electrodes” or the like.

The calibration datastore 204 stores data in the form of a calibrationtable that correlates the unique identifier of the test housing 130 withcalibration data 258 for the particular test housing 130. Thus, thecalibration datastore 204 stores one or more lookup tables, whichprovide calibration data 258 that corresponds with unique identifier ofthe test housing 130 received from the test device data 226. In oneexample, the calibration data 258 stored in the calibration datastore204 is populated based on the test device calibration data 268 by thecalibration control module 206 during a calibration test. It should benoted, however, that the calibration data 258 stored in the calibrationdatastore 204 may be pre-defined, or default values.

The calibration control module 206 receives as input the calibrationtest command 224 from the UI control module 202. Based on the receipt ofthe calibration test command 224, the calibration control module 206receives as input the test fluid quantity data 230 and the test devicedata 226 from the UI control module 202. The calibration control module206 sets a counter equal to zero. The calibration control module 206outputs voltage data 262. The voltage data 262 is one or more controlsignals to the power source 112 to alternate and apply the voltage tothe respective input electrodes 132 a-132 j. Based on the output of thevoltage data 262, the calibration control module 206 receives as inputactivation data 264. The activation data 264 is the signal received fromthe respective one of the output electrodes 134 a-134 j based on thevoltage potential created by the voltage applied to the respective inputelectrode 132 a-132 j that when the fluid 118 is present causes thecurrent to pass through the fluid 118 within the internal channel 152(FIG. 3) to the respective output electrode 134 a-134 j. In one example,the calibration control module 206 determines, based on the activationdata 264, whether the output electrode 134 a and/or the output electrode134 b has been activated such that the voltage applied to the inputelectrode 132 a has caused current to pass through the fluid 118 in theinternal channel 152 to the respective output electrode 134 a and/or 134b, which indicates that the test housing 130 has been primed with thefluid 118. The calibration control module 206 also determines, based onthe activation data 264, which of the output electrodes 134 a-134 j isactivated by the fluid 118 flowing within the internal channel 152 (FIG.3). Based on the current increment of the counter, the calibrationcontrol module 206 determines which pre-defined volume of fluid wasreceived into the test housing 130 based on the test fluid quantity data230. In this regard, as the test fluid quantity data 230 generallyincludes an ordered listing of the pre-defined volumes of fluid to bereceived into the test housing 130, the calibration control module 206determines which pre-defined volume of fluid was received based on thecount of the counter.

The calibration control module 206 associates the identified pre-definedvolume of fluid received into the test housing 130 with the respectiveone or more of the activated output electrode 134 a-134 j for theparticular test housing 130 identified in the test device data 226, andstores this data as test device calibration data 268 in the calibrationdatastore 204. The calibration control module 206 determines whethereach of the output electrodes 134 a-134 j has been activated. Thecalibration control module 206 repeats this process until each of theoutput electrodes 134 a-134 j has been activated. If each of the outputelectrodes 134 a-134 j has been activated, the calibration controlmodule 206 outputs stop voltage command 270. The stop voltage command270 is one or more control signals to the power source 112 to stop theapplication of the voltage to the input electrodes 132 a-132 j. Thecalibration control module 206 also sets the test device calibrationdata 268 for the UI control module 202. Generally, the test devicecalibration data 268 indicates a known volume of fluid to activate eachoutput electrode 134 a-134 j in the internal channel 152 over an entirelength of the internal channel 152.

For example, a delivery amount of 250 nanolitres (nL) is designed tocover or activate 10 output electrodes 134 a-134 j. While delivering thecalibrated amount of 250 nanolitres (nL) during an exemplary calibrationtest, nine output electrodes 134 a-134 j are determined to be activated.The calibration control module 206 determines that nine outputelectrodes 134 a-134 j are activated per 250 nanolitres (nL) and setsthis as the test device calibration data 268.

With reference to FIG. 5, a dataflow diagram illustrates variousembodiments of the test control module 208 of the test control system200, which may be embedded within the controller 114. Variousembodiments of the test control module 208 according to the presentdisclosure can include any number of sub-modules embedded within thecontroller 114. As can be appreciated, the sub-modules shown in FIG. 5may be combined and/or further partitioned to similarly control theinput electrodes 132 a-132 j and determine an amount of fluid dispensedby the fluid infusion device 102 based on the activated output electrode134 a-134 j. In various embodiments, the test control module 208includes a test device manager module 400, an electrode control module402, a bolus datastore 404, a bolus monitor module 406, a basaldatastore 408 and a basal monitor module 410.

The test device manager module 400 receives as input test device data226 from the UI control module 202 (FIGS. 4A and 4B). Based on the testdevice data 226, the test device manager module 400 queries thecalibration datastore 204 (FIGS. 4A and 4B), and retrieves thecalibration data 258 associated with the unique identifier of the testhousing 130 (from the test device data 226). The test device managermodule 400 sets the test device data 226 and the calibration data 258 ashousing data 412 for the bolus monitor module 406 and the basal monitormodule 410. The housing data 412 includes the calibration data 258associated with the identified test housing 130, along with the distanceD between each of the input electrodes 132 a-132 j and each of theoutput electrodes 134 a-134 j, respectively, of the test housing 130,the radius R_(c) of the cross-sectional area of the internal channel 152or the cross-sectional area A_(c) of the internal channel 152, thethickness of the input electrodes 132 a-132 j, the manufacturingtolerance associated with the spacing between each of the inputelectrodes 132 a-132 j and each of the output electrodes 134 a-134 j,respectively, the manufacturing tolerance associated with the radiusR_(c) of the cross-sectional area of the internal channel 152 or amanufacturing tolerance associated with the cross-sectional area of theinternal channel 152 (such as a manufacturing tolerance associated witha height and a width of the internal channel 152), and the data samplingrate associated with the output electrodes 134 a-134 j.

The electrode control module 402 receives as input a start command 414from the bolus monitor module 406 or the basal monitor module 410. Thestart command 414 is an instruction to apply a voltage to the inputelectrodes 132 a-132 j. Based on the start command 414, the electrodecontrol module 402 outputs the voltage data 262 to the power source 112.The electrode control module 402 also receives as input a stop command416 from the bolus monitor module 406 or the basal monitor module 410.The stop command 416 is an instruction to stop applying a voltage to theinput electrodes 132 a-132 j. Based on the stop command 416, theelectrode control module 402 outputs the stop voltage command 270 to thepower source 112.

The bolus datastore 404 stores the bolus activation data 248 associatedwith a bolus test. Thus, the bolus datastore 404 stores one or moretables, which provide the bolus activation data 248 that correspondswith a particular discrete volume of fluid or bolus dispensed into thetest housing 130. In one example, the bolus activation data 248 storedin the bolus datastore 404 is populated by the bolus monitor module 406during a bolus test.

The bolus monitor module 406 receives as input the bolus test command220 from the UI control module 202. Based on the receipt of the bolustest command 220, the bolus monitor module 406 sets the start command414 for the electrode control module 402, and sets a value of a counteras equal to one. In one example, the bolus monitor module 406 may alsoset the bolus prompt 255 for the UI control module 202 to instruct theuser to dispense the bolus into the test housing 130, and may determineif the bolus delivered command 261 has been received from the UI controlmodule 202. The bolus monitor module 406 receives as input theactivation data 264. In one example, the bolus monitor module 406determines, based on the activation data 264, whether the outputelectrode 134 a and/or the output electrode 134 b has been activatedsuch that the voltage applied to the input electrode 132 a has causedcurrent to pass through the fluid 118 in the internal channel 152 to therespective output electrode 134 a and/or 134 b, which indicates that thetest housing 130 has been primed with the fluid 118.

The bolus monitor module 406 also receives as input time data 266 andthe test fluid quantity data 230. The time data 266 is a current time,which may be received from other modules associated with the testcontrol module 208, such as an internal clock associated with theprocessor 180. The bolus monitor module 406 also determines, based onthe activation data 264 and the time data 266, which of the outputelectrodes 134 a-134 j have been activated by the fluid 118 receivedinto the internal channel 152 and at what time. Based on the currentincrement of the counter and the test fluid quantity data 230, the bolusmonitor module 406 determines which volume of fluid was received intothe test housing 130. The bolus monitor module 406 associates thedelivery of the fluid with the activated output electrodes 134 a-134 j,and stores this as the bolus activation data 248 in the bolus datastore404. The bolus monitor module 406 also sets the bolus activation data248 for the UI control module 202 (FIGS. 4A and 4B).

The bolus monitor module 406 also receives as input the housing data412. Based on the housing data 412 and the activation data 264, thebolus monitor module 406 determines the bolus amount data 232. In oneexample, the bolus monitor module 406 uses the following equation todetermine the volume of fluid received from the fluid infusion device102 for the bolus:

(A _(c) ±x ₁)((D+x ₂)+W _(e))=V  (2)

Wherein, A_(c) is the cross-sectional area of the internal channel 152in millimeters (mm); x₁ is the manufacturing tolerance associated withthe cross-sectional area of the internal channel 152, which in oneexample, is a manufacturing tolerance associated with the width and theheight of the internal channel 152 (in the example of a cylindricalinternal channel 152, x₁ is the manufacturing tolerance associated withthe radius (R_(c)) of the internal channel 152); D is the distancebetween each of the input electrodes 132 a-132 j and each of outputelectrodes 134 a-134 j, respectively, of the test housing 130 (measuredbetween respective ends 174 a-174 j; 176 a-176 j, which in this exampleis the same) in millimeters (mm); x₂ is the manufacturing toleranceassociated with the spacing between each of the input electrodes 132a-132 j and each of the output electrodes 134 a-134 j, respectively;W_(e) is the thickness of the input electrodes 132 a-132 j and theoutput electrodes 134 a-134 j in millimeters (mm); and V is the discretevolume of fluid observed by the output electrode 134 a-134 j in cubicmillimeters (mm³). In this example, A_(c), D, x₁, x₂ and W_(e) are allpre-determined or pre-defined known values that are received as housingdata 412. In one example, the A_(c) is the cross-sectional area of theinternal channel 152 and in this example, A_(c)=π(R_(c))², wherein R_(c)is the pre-defined known value of the radius of the internal channel152. In this example, A_(c) of the internal channel 152 may becalculated by the processor 180 based on the known value of R_(c), whichis received in the housing data 412. By having current pass through agiven output electrode 134 a-134 j, the bolus monitor module 406determines how far the fluid 118 has traveled and, based on equation (2)and the calibration data 258, calculates how much volume of fluid hasbeen delivered. In this regard, based on the calibration data 258retrieved with the housing data 412, the bolus monitor module 406compares the determined volume V of fluid from equation (2) with thecalibration data 258 and determines the volume of fluid delivered.Referencing the prior example, if nine output electrodes 134 a-134 jhave been activated, the bolus monitor module 406 determines that 250nanolitres (nL) has been delivered. The bolus monitor module 406associates the volume of fluid delivered with the particular pre-definedvolume of fluid or bolus received (based on the count of the counter) asthe bolus amount data 232 for the UI control module 202 (FIGS. 4A and4B).

Based on the bolus amount data 232 and the test fluid quantity data 230,the bolus monitor module 406 determines the bolus error data 236. In oneexample, the bolus monitor module 406 divides the determined volume offluid delivered with the expected volume of fluid received as input inthe test fluid quantity data 230 and multiplies the value by 100 toarrive at a percent error for the particular bolus received from thefluid infusion device 102. The bolus monitor module 406 sets the boluserror data 236 for the UI control module 202 (FIGS. 4A and 4B).

After determining the volume of fluid delivered, the bolus monitormodule 406 increments the counter by one. The bolus monitor module 406determines whether the counter is greater than a pre-defined thresholdcount. In one example, the pre-defined threshold count is about 25. Ifthe counter is less than the pre-defined threshold count, the bolusmonitor module 406 sets bolus prompt 255 for the UI control module 202.

Once the bolus monitor module 406 ceases to receive activation data 264such that the output electrodes 134 a-134 j are no longer beingactivated, the bolus monitor module 406 sets the stop command 416 forthe electrode control module 402. The bolus monitor module 406 may alsoset the error flag 259 for the UI control module 202 based on activationdata 264 not being received from one or more of the output electrodes134 a-134 j.

The basal datastore 408 stores the basal activation data 252 associatedwith a basal test. Thus, the basal datastore 408 stores one or moretables, which provide the basal activation data 252 that correspondswith a particular volume of fluid received over a period of time orbasal rate dispensed into the test housing 130. In one example, thebasal activation data 252 stored in the basal datastore 408 is populatedby the basal monitor module 410 during a basal test.

The basal monitor module 410 receives as input the basal test command222 from the UI control module 202. Based on the receipt of the basaltest command 222, the basal monitor module 410 sets the start command414 for the electrode control module 402, and sets a value of a timer asequal to zero. The basal monitor module 410 receives as input theactivation data 264. In one example, the basal monitor module 410determines, based on the activation data 264, whether the outputelectrode 134 a and/or the output electrode 134 b has been activatedsuch that the voltage applied to the input electrode 132 a has causedcurrent to pass through the fluid 118 in the internal channel 152 to therespective output electrode 134 a and/or 134 b, which indicates that thetest housing 130 has been primed with the fluid 118.

The basal monitor module 410 also receives as input the time data 266and the rate data 228. The basal monitor module 410 determines, based onthe activation data 264 and the time data 266, which of the outputelectrodes 134 a-134 j have been activated by the fluid 118 receivedinto the internal channel 152 and at what time by a particularshotcycle. Based on the current time of the timer, the basal monitormodule 410 associates the delivery of the fluid 118 with the activatedoutput electrodes 134 a-134 j, and stores this as the basal activationdata 252 in the basal datastore 408. Generally, the particular shotcycleis determined based on the fluid infusion device 102 being employed withthe test system 100 and the repeating patterns of discrete fluiddeliveries the fluid infusion device 102 may employ or the smallestamount of time and volume that is desired to be evaluated for a givenbasal rate. The shotcycles associated with the particular fluid infusiondevice 102 and/or the smallest of amount of time and volume that isdesired to be evaluated may be received as input data from the operator,or may be pre-defined and stored in the memory 182 associated with theprocessor 180. The basal monitor module 410 also sets the basalactivation data 252 for the UI control module 202 (FIGS. 4A and 4B).

The basal monitor module 410 also receives as input the housing data412. Based on the housing data 412 and the activation data 264, thebasal monitor module 410 determines the basal rate data 240. In oneexample, the basal monitor module 410 uses equation (3), below, todetermine the volume of fluid received from the fluid infusion device102 over a period of time:

$\begin{matrix}{\frac{\left( {A_{c} \pm x_{1}} \right)\left( {\left( {D \pm x_{2}} \right) + W_{e}} \right)}{t} = V_{r}} & (3)\end{matrix}$

Wherein, A_(c) is the cross-sectional area of the internal channel 152in millimeters (mm); x₁ is the manufacturing tolerance associated withthe cross-sectional area of the internal channel 152, which in oneexample, is a manufacturing tolerance associated with the width and theheight of the internal channel 152 (in the example of a cylindricalinternal channel 152, x₁ is the manufacturing tolerance associated withthe radius (R_(c)) of the internal channel 152); D is the distancebetween each of the input electrodes 132 a-132 j and each of the outputelectrodes 134 a-134 j, respectively, of the test housing 130 (measuredbetween respective ends 174 a-174 j; 176 a-176 j, which in this exampleis the same) in millimeters (mm); x₂ is the manufacturing toleranceassociated with the spacing between each of the input electrodes 132a-132 j and each of the output electrodes 134 a-134 j, respectively;W_(e) is the thickness of the input electrodes 132 a-132 j and theoutput electrodes 134 a-134 j in millimeters (mm); t is the time of thetimer (in seconds) and V_(r) is the volume of fluid observed by theoutput electrode 134 a-134 j per the period of time measured by thetimer in cubic millimeters per second (mm³/s). As discussed with regardto equation (2), A_(c), D, x₁, x₂ and W_(e) are all pre-determined orpre-defined known values. In one example, the A_(c) is thecross-sectional area of the internal channel 152 and in this example,A_(c)=π(R_(c))², wherein R_(c) is the pre-defined known value of theradius of the internal channel 152. In this example, A_(c) of theinternal channel 152 may be calculated by the processor 180 based on theknown value of R_(c), which is received in the housing data 412.

By having current pass through a given output electrode 134 a-134 j, thebasal monitor module 410 determines how far the fluid 118 has traveledand, based on equation (3) and the calibration data 258, calculates howmuch volume of fluid has been delivered per unit time. In this regard,based on the calibration data 258 retrieved with the housing data 412,the basal monitor module 410 compares the determined volume of fluid perperiod of time from equation (3) with the calibration data 258 anddetermines the volume of fluid delivered per period of time. The basalmonitor module 410 sets the determined volume delivered per period oftime as the basal rate data 240 for the UI control module 202 (FIGS. 4Aand 4B).

Based on the basal rate data 240 and the rate data 228, the basalmonitor module 410 determines the basal error data 244. In one example,the basal monitor module 410 determines the basal error data 235 basedequation (4), below:

$\begin{matrix}{{Error_{i}} = {\left( \frac{\frac{{Vr_{i + \frac{P}{S}}} - {Vr}_{i}}{t_{i + \frac{P}{S}} - t_{i}} - \gamma}{r} \right)*100\%}} & (4)\end{matrix}$

Wherein Vr_(i) is the volume at a given data point (i) in cubicmillimeters (mm³) as determined from equation (3); t is the time elapsedat the given data point as measured by the timer; P is one hour inseconds (s); S is the data sampling rate of the output electrodes 134a-134 j, which is received from the housing data 412; r is the inputbasal rate or the rate data 228 in microliters per hour (μL/h); andError_(i) is the overall error value for the dispensing of the fluid bythe fluid infusion device 102 over the period of time in percent (%).Generally, the basal rate data 240 calculates the Error_(i) value for aplurality of data points over a basal test, and in one example, eachdata point equal to about one hour of the particular basal test for a 24hour basal test. The basal monitor module 410 also determines themaximum error for the basal test, which is the largest calculatedError_(i) value for the basal test. The basal monitor module 410determines the minimum error for the basal test, which is the smallestcalculated Error_(i) value for the basal test. The basal monitor module410 sets the Error_(i) value determined for the data point, along withthe maximum error and the minimum error as the basal rate data 240 forthe UI control module 202 (FIGS. 4A and 4B).

After determining the volume of fluid delivered per time, the basalmonitor module 410 determines whether each of the output electrodes 134a-134 j has been activated in the internal channel 152 of the testhousing 130. If true, the basal monitor module 410 sets the stop command416 for the electrode control module 402. Otherwise, the basal monitormodule 410 determines whether the end test command 263 has been receivedas input from the UI control module 202. If the end test command 263 hasbeen received, the basal monitor module 410 sets the stop command 416.Otherwise, the basal monitor module 410 continues to monitor for theactivation data 264.

Referring now to FIG. 10, and with continued reference to FIGS. 1-5, aflowchart illustrates a control method 500 that can be performed by thetest control system 200 of FIGS. 1-5 in accordance with the presentdisclosure. In various embodiments, the control method 500 is performedby the processor 180 of the controller 114. As can be appreciated inlight of the disclosure, the order of operation within the method is notlimited to the sequential execution as illustrated in FIG. 10, but maybe performed in one or more varying orders as applicable and inaccordance with the present disclosure. In various embodiments, thecontrol method 500 can be scheduled to run based on one or morepredetermined events, and/or can run continuously during operation ofthe test system 100.

The method begins at 502. At 504, the method determines whether inputdata 210 has been received from the user's manipulation of the inputdevice 108. If input data 210 has been received, the method proceeds to506. Otherwise, the method loops.

At 506, the method receives and processes the input data 210 todetermine the type of test (test type input data 212), the expectedpre-defined volumes of fluid that are to be received the particularnumber of times (fluid quantity input data 218), data associated withthe particular test device (test device input data 214) and the set rate(set rate input data 216). At 508, the method determines whether thetest type input data 212 is a calibration test. If true, the methodproceeds to 510. Otherwise, at 512, the method determines whether thetest type input data 212 is a bolus test. If true, the method proceedsto 514. Otherwise, at 516, the method determines whether the test typeinput data 212 is a basal test. If true, the method proceeds to 518.Otherwise, the method flags an error at 520 and ends at 522. Optionally,the method may loop from 516 to 504.

At 510, the method proceeds to start a calibration test, as will bediscussed with regard to FIG. 11. With the determination of a bolustest, at 514, the method retrieves the calibration data 258 associatedwith the particular test device (based on the test device input data214) and at 524, the method proceeds to start a bolus test, as will bediscussed with regard to FIG. 12. With the determination of a basaltest, at 518, the method retrieves the calibration data 258 associatedwith the particular test device (based on the test device input data214) and at 526, the method proceeds to start a basal test, as will bediscussed with regard to FIG. 13.

Referring now to FIG. 11, and with continued reference to FIGS. 1-5, aflowchart illustrates a calibration method 600 that can be performed bythe test control system 200 of FIGS. 1-5 in accordance with the presentdisclosure. In various embodiments, the calibration method 600 isperformed by the processor 180 of the controller 114. As can beappreciated in light of the disclosure, the order of operation withinthe method is not limited to the sequential execution as illustrated inFIG. 11, but may be performed in one or more varying orders asapplicable and in accordance with the present disclosure. In variousembodiments, the calibration method 600 can be scheduled to run based onone or more predetermined events, such as based on the receipt of theinput data 210. Prior to beginning the calibration method, the operatorinputs commands to a user interface of the fluid infusion device 102 toprime the fluid infusion device 102 and the test housing 130.

The method begins at 602. At 606, the method commands the power source112 to apply a voltage to alternating ones of the input electrodes 132a-132 j of the fluid delivery test device 106 or outputs the voltagedata 262 to the power source 112. At 607, the method determines, basedon the activation data 264, whether the output electrode 134 a and/orthe output electrode 134 b has been activated such that the voltageapplied to the input electrode 132 a has caused current to pass throughthe fluid 118 in the internal channel 152 to the respective outputelectrode 134 a and/or 134 b, which indicates that the test housing 130has been primed with the fluid 118. If the output electrodes 134 aand/or 134 b are not activated, the method loops until the outputelectrodes 134 a and/or 134 b are activated. Otherwise, at 609, themethod sets a counter to a value equal to zero.

At 608, the method determines, based on the activation data 264, whetherone or more of the output electrodes 134 a-134 j have been activatedsuch that the voltage applied to the respective input electrode 132a-132 j has caused current to pass through the fluid 118 in the internalchannel 152 to the respective output electrode 134 a-134 j. If one ormore of the output electrodes 134 a-134 j are not activated, the methodloops until one or more of the output electrodes 134 a-134 j areactivated.

If one or more of the output electrodes 134 a-134 j are determined to beactivated, based on the receipt of activation data 264, at 610, themethod determines which of the output electrodes 134 a-134 j isactivated by the fluid 118 flowing within the internal channel 152 (FIG.2). At 612, the method determines, based on the current increment of thecounter, which pre-defined volume of fluid was received into the testhousing 130 based on the test fluid quantity data 230 received as inputdata 210. At 614, the method associates the identified pre-definedvolume of fluid received into the test housing 130 with the respectiveone or more of the activated output electrode 134 a-134 j for theparticular test housing 130 identified in the test device data 226, andstores this data as test device calibration data 268 in the calibrationdatastore 204.

At 616, the method determines whether each of the output electrodes 134a-134 j in the test housing 130 has been activated based on theactivation data 264 that has been received. If true, the method proceedsto 618. Otherwise, the method proceeds to 620. At 620, the methodincrements the counter by one and loops to 608.

At 618, the method commands the power source 112 to cease applying thevoltage to alternating ones of the input electrodes 132 a-132 j of thefluid delivery test device 106 or outputs the stop voltage command 270to the power source 112. The method ends at 622.

Referring now to FIG. 12, and with continued reference to FIGS. 1-5, aflowchart illustrates a bolus test method 700 that can be performed bythe test control system 200 of FIGS. 1-5 in accordance with the presentdisclosure. In various embodiments, the bolus test method 700 isperformed by the processor 180 of the controller 114. As can beappreciated in light of the disclosure, the order of operation withinthe method is not limited to the sequential execution as illustrated inFIG. 12, but may be performed in one or more varying orders asapplicable and in accordance with the present disclosure. In variousembodiments, the bolus test method 700 can be scheduled to run based onone or more predetermined events, such as based on the receipt of theinput data 210. Prior to beginning the bolus test method, the operatorinputs commands to a user interface of the fluid infusion device 102 toprime the fluid infusion device 102 and the test housing 130.

The method begins at 702. At 704, the method commands the power source112 to apply a voltage to alternating ones of the input electrodes 132a-132 j of the fluid delivery test device 106 or outputs the voltagedata 262 to the power source 112. At 705, the method determines, basedon the activation data 264, whether the output electrode 134 a and/orthe output electrode 134 b has been activated such that the voltageapplied to the input electrode 132 a has caused current to pass throughthe fluid 118 in the internal channel 152 to the respective outputelectrode 134 a and/or 134 b, which indicates that the test housing 130has been primed with the fluid 118. If the output electrodes 134 aand/or 134 b are not activated, the method loops until the outputelectrodes 134 a and/or 134 b are activated.

At 706, the method sets a counter to a value equal to zero, andoptionally, outputs the prompt user interface 257 to instruct the userto dispense the bolus. At 707, optionally, the method determines, basedon the bolus delivery data 217, whether the bolus has been delivered. Iftrue, the method proceeds to 708. Otherwise, if false, the method loops.

At 708, the method determines, based on the activation data 264, whetherone or more of the output electrodes 134 a-134 j have been activatedsuch that the voltage applied to the respective input electrode 132a-132 j has caused current to pass through the fluid 118 in the internalchannel 152 to the respective output electrode 134 a-134 j. If one ormore of the output electrodes 134 a-134 j are not activated, the methodproceeds to 710. At 710, the method commands the power source 112 tocease applying the voltage to alternating ones of the input electrodes132 a-132 j of the fluid delivery test device 106 or outputs the stopvoltage command 270 to the power source 112. The method flags an errorat 712. The method ends at 714.

Otherwise, if one or more of the output electrodes 134 a-134 j aredetermined to be activated, based on the receipt of activation data 264,at 716, the method determines which of the output electrodes 134 a-134 jis activated by the fluid 118 flowing within the internal channel 152(FIG. 2) and at what time based on time data 266 received from othermodules associated with the controller 114. At 718, the methoddetermines, based on the current increment of the counter, which volumeof fluid was received into the test housing 130 based on the test fluidquantity data 230 received as input data 210. At 719, the methodassociates the identified volume of fluid received into the test housing130 with the respective one or more of the activated output electrodes134 a-134 j at the current time for the particular test housing 130identified in the test device data 226, and stores this data as bolusactivation data 248 in the bolus datastore 404.

At 720, the method determines a volume of fluid delivered by the fluidinfusion device 102 based on equation (2), the calibration data 258, thetest device data 226 and the output electrodes 134 a-134 j that wereactivated. At 722, the method determines the bolus error data 236. At724, the method outputs the bolus activation user interface 250 thatillustrates when the output electrodes 134 a-134 j were activated at aparticular time based on the received fluid or bolus delivered by thefluid infusion device 102. At 726, the method outputs the bolus amountuser interface 234 that illustrates the volume of fluid or bolusdelivered by the fluid infusion device 102 for the particular count ofthe counter and outputs the bolus error user interface 238 thatillustrates the error associated with each volume of fluid or bolusdelivered by the fluid infusion device 102 for the particular count ofthe counter.

At 728, the method increments the counter by one. At 730, the methoddetermines whether the counter is less than the pre-defined thresholdcount. If the counter is less than the pre-defined threshold count, at732, the method outputs the prompt user interface 257 and proceeds to707. Otherwise, if the counter is greater than the pre-defined thresholdcount, the method proceeds to 710.

Referring now to FIG. 13, and with continued reference to FIGS. 1-5, aflowchart illustrates a basal test method 800 that can be performed bythe test control system 200 of FIGS. 1-5 in accordance with the presentdisclosure. In various embodiments, the basal test method 800 isperformed by the processor 180 of the controller 114. As can beappreciated in light of the disclosure, the order of operation withinthe method is not limited to the sequential execution as illustrated inFIG. 13, but may be performed in one or more varying orders asapplicable and in accordance with the present disclosure. In variousembodiments, the basal test method 800 can be scheduled to run based onone or more predetermined events, such as based on the receipt of theinput data 210. Prior to beginning the basal test method, the operatorinputs commands to a user interface of the fluid infusion device 102 toprime the fluid infusion device 102 and the test housing 130.

The method begins at 802. At 804, the method commands the power source112 to apply a voltage to alternating ones of the input electrodes 132a-132 j of the fluid delivery test device 106 or outputs the voltagedata 262 to the power source 112. At 805, the method determines, basedon the activation data 264, whether the output electrode 134 a and/orthe output electrode 134 b has been activated such that the voltageapplied to the input electrode 132 a has caused current to pass throughthe fluid 118 in the internal channel 152 to the respective outputelectrode 134 a and/or 134 b, which indicates that the test housing 130has been primed with the fluid 118. If the output electrodes 134 aand/or 134 b are not activated, the method loops until the outputelectrodes 134 a and/or 134 b are activated.

At 806, the method sets a timer to a value equal to zero. At 808, themethod determines, based on the activation data 264, whether one or moreof the output electrodes 134 a-134 j have been activated such that thevoltage applied to the respective input electrode 132 a-132 j has causedcurrent to pass through the fluid 118 in the internal channel 152 to therespective output electrode 134 a-134 j. If one or more of the outputelectrodes 134 a-134 j are not activated, the method loops.

Otherwise, if one or more of the output electrodes 134 a-134 j aredetermined to be activated, based on the receipt of activation data 264,at 810, the method determines which of the output electrodes 134 a-134 jis activated by the fluid 118 flowing within the internal channel 152(FIG. 2) and at what time based on time data 266 received from othermodules associated with the controller 114. At 812, the methodassociates the volume of fluid received into the test housing 130 withthe respective one or more of the activated output electrodes 134 a-134j at the current time of the timer, and stores this data as basalactivation data 252 in the basal datastore 408.

At 814, the method determines a volume of fluid delivered by the fluidinfusion device 102 per time based on equation (3), the calibration data258, the test device data 226, the value of the timer and the outputelectrodes 134 a-134 j that were activated. At 816, the methoddetermines the basal error data 244 using equation (4). At 818, themethod outputs the basal activation user interface 254 that illustrateswhen the output electrodes 134 a-134 j were activated at a particulartime based on the fluid delivered by the fluid infusion device 102. At820, the method outputs the basal rate user interface 242 thatillustrates the volume of fluid or bolus delivered by the fluid infusiondevice 102 over the time measured by the timer and outputs the basalerror user interface 246 that illustrates the error associated with theamount of fluid received from the fluid infusion device 102 over thetime measured by the timer.

At 822, the method determines whether each of the output electrodes 134a-134 j in the test housing 130 has been activated based on theactivation data 264 that has been received. If true, the method proceedsto 824. At 824, the method commands the power source 112 to ceaseapplying the voltage to alternating ones of the input electrodes 132a-132 j of the fluid delivery test device 106 or outputs the stopvoltage command 270 to the power source 112. The method ends at 826.

Otherwise, if each of the output electrodes 134 a-134 j have not beenactivated, the method proceeds to 828. At 828, the method determineswhether the end test data 219 has been received in the input data 210.If true, the method proceeds to 824. Otherwise, the method loops to 808.

While at least one exemplary embodiment has been presented in theforegoing detailed description, it should be appreciated that a vastnumber of variations exist. It should also be appreciated that theexemplary embodiment or embodiments described herein are not intended tolimit the scope, applicability, or configuration of the claimed subjectmatter in any way. Rather, the foregoing detailed description willprovide those skilled in the art with a convenient road map forimplementing the described embodiment or embodiments. It should beunderstood that various changes can be made in the function andarrangement of elements without departing from the scope defined by theclaims, which includes known equivalents and foreseeable equivalents atthe time of filing this patent application.

What is claimed is:
 1. A processor-implemented method comprising:processing a signal indicative of activation of an output electrode of aplurality of output electrodes positioned along a dimension of a fluidchannel, each output electrode of the plurality of output electrodescorresponding to a respective input electrode of a plurality of inputelectrodes positioned along the dimension of the fluid channel, theactivation of the output electrode being caused by electrical currentconducted between the output electrode and a corresponding inputelectrode through fluid that accumulates along the dimension of thefluid channel as the fluid is dispensed into the fluid channel;identifying which output electrode, of the plurality of outputelectrodes, was activated to cause generation of the signal; calculatinga volume of the fluid dispensed into the fluid channel based on arelative position of the identified output electrode along the dimensionof the fluid channel.
 2. The method of claim 1, further comprising:causing display of data representative of the volume of the fluiddispensed into the fluid channel.
 3. The method of claim 1, furthercomprising: supplying electrical current to the plurality of inputelectrodes in an alternating pattern.
 4. The method of claim 1, furthercomprising: supplying electrical current to the plurality of inputelectrodes in a sequential pattern.
 5. The method of claim 1, furthercomprising: calculating, based on an expected volume of the fluiddispensed into the fluid channel, an error associated with thecalculated volume of the fluid dispensed into the fluid channel.
 6. Themethod of claim 1, further comprising: calculating a rate at which thefluid was dispensed into the fluid channel based on the calculatedvolume and a period of time during which the fluid was dispensed intothe fluid channel; and calculating, based on an expected rate at whichthe fluid was to be dispensed into the fluid channel, an errorassociated with the calculated rate at which the fluid was dispensedinto the fluid channel.
 7. The method of claim 1, wherein processing thesignal indicative of activation of the output electrode includesdetermining that the fluid is present at the output electrode based on acomparison of the signal to a reference metric.
 8. The method of claim1, wherein calculating the volume of the fluid includes: determining ameasurement of a dimension of the volume of the fluid based on therelative position of the identified output electrode along the dimensionof the fluid channel, the dimension of the volume of the fluid beingparallel to the dimension of the fluid channel.
 9. One or morenon-transitory processor-readable media storing instructions which, whenexecuted by one or more processors, cause performance of: processing asignal indicative of activation of an output electrode of a plurality ofoutput electrodes positioned along a dimension of a fluid channel, eachoutput electrode of the plurality of output electrodes corresponding toa respective input electrode of a plurality of input electrodespositioned along the dimension of the fluid channel, the activation ofthe output electrode being caused by electrical current conductedbetween the output electrode and a corresponding input electrode throughfluid that accumulates along the dimension of the fluid channel as thefluid is dispensed into the fluid channel; identifying which outputelectrode, of the plurality of output electrodes, was activated to causegeneration of the signal; calculating a volume of the fluid dispensedinto the fluid channel based on a relative position of the identifiedoutput electrode along the dimension of the fluid channel.
 10. The oneor more non-transitory processor-readable media of claim 9, furtherstoring instructions which, when executed by the one or more processors,cause performance of: causing display of data representative of thevolume of the fluid dispensed into the fluid channel.
 11. The one ormore non-transitory processor-readable media of claim 9, further storinginstructions which, when executed by the one or more processors, causeperformance of: supplying electrical current to the plurality of inputelectrodes in an alternating pattern.
 12. The one or more non-transitoryprocessor-readable media of claim 9, further storing instructions which,when executed by the one or more processors, cause performance of:supplying electrical current to the plurality of input electrodes in asequential pattern.
 13. The one or more non-transitoryprocessor-readable media of claim 9, further storing instructions which,when executed by the one or more processors, cause performance of:calculating, based on an expected volume of the fluid dispensed into thefluid channel, an error associated with the calculated volume of thefluid dispensed into the fluid channel.
 14. The one or morenon-transitory processor-readable media of claim 9, further storinginstructions which, when executed by the one or more processors, causeperformance of: calculating a rate at which the fluid was dispensed intothe fluid channel based on the calculated volume and a period of timeduring which the fluid was dispensed into the fluid channel; andcalculating, based on an expected rate at which the fluid was to bedispensed into the fluid channel, an error associated with thecalculated rate at which the fluid was dispensed into the fluid channel.15. A system comprising: one or more processors; and one or moreprocessor-readable media storing instructions which, when executed bythe one or more processors, cause performance of: processing a signalindicative of activation of an output electrode of a plurality of outputelectrodes positioned along a dimension of a fluid channel, each outputelectrode of the plurality of output electrodes corresponding to arespective input electrode of a plurality of input electrodes positionedalong the dimension of the fluid channel, the activation of the outputelectrode being caused by electrical current conducted between theoutput electrode and a corresponding input electrode through fluid thataccumulates along the dimension of the fluid channel as the fluid isdispensed into the fluid channel; identifying which output electrode, ofthe plurality of output electrodes, was activated to cause generation ofthe signal; calculating a volume of the fluid dispensed into the fluidchannel based on a relative position of the identified output electrodealong the dimension of the fluid channel.
 16. The system of claim 15,wherein the one or more processor-readable media further storeinstructions which, when executed by the one or more processors, causeperformance of: causing display of data representative of the volume ofthe fluid dispensed into the fluid channel.
 17. The system of claim 15,wherein the one or more processor-readable media further storeinstructions which, when executed by the one or more processors, causeperformance of: supplying electrical current to the plurality of inputelectrodes in an alternating pattern.
 18. The system of claim 15,wherein the one or more processor-readable media further storeinstructions which, when executed by the one or more processors, causeperformance of: supplying electrical current to the plurality of inputelectrodes in a sequential pattern.
 19. The system of claim 15, whereinthe one or more processor-readable media further store instructionswhich, when executed by the one or more processors, cause performanceof: calculating, based on an expected volume of the fluid dispensed intothe fluid channel, an error associated with the calculated volume of thefluid dispensed into the fluid channel.
 20. The system of claim 15,wherein the one or more processor-readable media further storeinstructions which, when executed by the one or more processors, causeperformance of: calculating a rate at which the fluid was dispensed intothe fluid channel based on the calculated volume and a period of timeduring which the fluid was dispensed into the fluid channel; andcalculating, based on an expected rate at which the fluid was to bedispensed into the fluid channel, an error associated with thecalculated rate at which the fluid was dispensed into the fluid channel.